U.S. patent number 9,339,252 [Application Number 14/200,989] was granted by the patent office on 2016-05-17 for x-ray ct imaging device and x-ray ct imaging method.
This patent grant is currently assigned to J. Morita Manufacturing Corporation. The grantee listed for this patent is J. Morita Manufacturing Corporation. Invention is credited to Yoshito Sugihara, Hideki Yoshikawa.
United States Patent |
9,339,252 |
Sugihara , et al. |
May 17, 2016 |
X-ray CT imaging device and X-ray CT imaging method
Abstract
According to an X-ray imaging device for performing CT imaging,
a main body control section controls at least one of an X-ray
revolution plane formed by an X-ray cone beam along with the
revolution of a revolving arm and a revolution range of the
revolving arm in accordance with a CT imaging area accepted by an
imaging area setting screen. Such control is performed in order to
decrease X-ray radiation to a high sensitivity site in the area
that revolves during the CT imaging, the high sensitivity site
being positionally set in a biological body as a site that is
sensitive to X-rays.
Inventors: |
Sugihara; Yoshito (Kyoto,
JP), Yoshikawa; Hideki (Kyoto, JP) |
Applicant: |
Name |
City |
State |
Country |
Type |
J. Morita Manufacturing Corporation |
Kyoto |
N/A |
JP |
|
|
Assignee: |
J. Morita Manufacturing
Corporation (Kyoto, JP)
|
Family
ID: |
50679819 |
Appl.
No.: |
14/200,989 |
Filed: |
March 7, 2014 |
Prior Publication Data
|
|
|
|
Document
Identifier |
Publication Date |
|
US 20140328446 A1 |
Nov 6, 2014 |
|
Foreign Application Priority Data
|
|
|
|
|
Mar 8, 2013 [JP] |
|
|
2013-046862 |
|
Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61B
6/501 (20130101); A61B 6/032 (20130101); A61B
6/14 (20130101); A61B 6/542 (20130101) |
Current International
Class: |
A61B
5/06 (20060101); A61B 6/03 (20060101); A61B
6/00 (20060101); G01N 23/04 (20060101); A61B
6/14 (20060101); A61B 5/08 (20060101) |
Field of
Search: |
;378/4,62,108,151,5,901,147,150,16 ;382/131,103,107,154
;250/336.1,361R |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
|
|
|
|
|
|
|
1393681 |
|
Mar 2004 |
|
EP |
|
H11-19078 |
|
Jan 1999 |
|
JP |
|
2003-245277 |
|
Sep 2003 |
|
JP |
|
2006-280478 |
|
Oct 2006 |
|
JP |
|
2007-029168 |
|
Feb 2007 |
|
JP |
|
2010-269048 |
|
Dec 2010 |
|
JP |
|
2011-041598 |
|
Mar 2011 |
|
JP |
|
2012/130542 |
|
Jul 2012 |
|
JP |
|
2012-217572 |
|
Nov 2012 |
|
JP |
|
03/084407 |
|
Oct 2003 |
|
WO |
|
2009063974 |
|
May 2009 |
|
WO |
|
Primary Examiner: Vanore; David A
Attorney, Agent or Firm: Osha Liang LLP
Claims
What is claimed is:
1. An X-ray CT imaging device, comprising: a revolution section
that causes an X-ray generation source and an electric X-ray
detector, facing each other while having a subject therebetween, to
revolve about a revolution shaft as a center of revolution; a
revolution driving section that drives driving the revolution
section to revolve with respect to the subject; an X-ray radiation
area setting section that accepts a setting of a local area of the
subject as an X-ray radiation area; a control section that controls
at least the revolution driving section; and a high sensitivity
site specification section to specify a high sensitivity site in a
biological body that is highly sensitive to an X-ray; wherein the
revolution section is revolved with respect to the X-ray radiation
area to perform CT imaging; and wherein, when radiation of an X-ray
flux in a revolving movement is performed during the CT imaging in
accordance with the X-ray radiation area accepted by the X-ray
radiation area setting section, the control section controls at
least one of an X-ray revolution plane formed by the X-ray flux
along with the revolution of the revolution section, and a
revolution range of the revolution section, such that an amount of
X-ray radiation toward the high sensitivity site is decreased.
2. An X-ray CT imaging device according to claim 1, wherein the
high sensitivity site specification section specifies the high
sensitivity site in a schematic view of a head of the subject.
3. An X-ray CT imaging device according to claim 1, wherein the
control section performs revolution range control of changing at
least one of an X-ray radiation start position and an X-ray
radiation end position in the revolution range in accordance with
the X-ray radiation area set by the X-ray radiation area setting
section and the high sensitivity site.
4. An X-ray CT imaging device according to claim 1, wherein the
control section performs control of changing at least one of an
X-ray radiation angle with respect to a predetermined reference
plane and a radiation position on the subject to control the x-ray
revolution plane in accordance with the X-ray radiation area set by
the X-ray radiation area setting section and the high sensitivity
site.
5. An X-ray CT imaging device according to claim 4, further
comprising: a support section that supports the revolution section
via the revolution shaft; and a support section moving section that
moves the support section; wherein the support section moving
section includes at least one of a shaft moving mechanism that
moves the revolution shaft with respect to the support section and
a relative moving mechanism that moves the support section with
respect to the subject; and wherein the control section controls
the movement of the support section moving section thus to control
the X-ray revolution plane.
6. An X-ray CT imaging device according to claim 4, further
comprising an X-ray radiation range restriction section that
restricts an X-ray radiation range, the X-ray radiation range
restriction section being provided forward to the X-ray generation
source in an X-ray radiation direction; wherein the control section
controls the restriction of the X-ray radiation range restriction
section thus to control the X-ray revolution plane.
7. An X-ray CT imaging device according to claim 1, further
comprising a control pattern storage section that stores a control
pattern by the control section for each of set areas that are each
set as the X-ray radiation area by the X-ray radiation area setting
section.
8. An X-ray CT imaging device according to claim 1, further
comprising a high sensitivity site information storage section that
stores information on the high sensitivity site.
9. An X-ray CT imaging device according to claim 1, wherein the
X-ray radiation area setting section displays an image containing
the X-ray radiation area and accepts a setting that sets the X-ray
radiation area with respect to the displayed image, and also
displays the high sensitivity site as overlapping the image.
10. An X-ray CT imaging device according to claim 9, further
comprising a high sensitivity site replacing section that replaces
the high sensitivity site displayed as overlapping the image with
another high sensitivity site.
11. An X-ray CT imaging device according to claim 1, further
comprising: an X-ray imaging preparation switch that revolves the
revolution section to the X-ray radiation start position in the
revolution range in accordance with the set area that is set by the
X-ray radiation area setting section, the revolution range being
different for each of the set areas; and an X-ray radiation switch
that directs the X-ray toward the set area while revolving the
revolution section to perform imaging.
12. An X-ray CT imaging device according to claim 1, further
comprising a movement driving section that moves the revolution
section; wherein the control section performs driving control that
moves the revolution section with respect to the movement driving
section; and wherein, in the driving control, controls for both of
the revolution of the revolution section and the movement of the
revolution section caused by moving the revolution shaft by the
movement driving section are performed concurrently to allow
panorama X-ray imaging to be performed.
13. An X-ray CT imaging device according to claim 1, further
comprising a cephalo-imaging head fixation device provided
perpendicularly to a direction of the revolution shaft, and thus
cephalo-X-ray imaging is allowed to be performed.
14. An X-ray CT imaging method performed by use of an X-ray CT
imaging device, the X-ray CT imaging device including: a revolution
section that causes an X-ray generation source and an electric
X-ray detector, facing each other while having a subject
therebetween, to revolve about a revolution shaft as a center of
revolution; a revolution driving section that drives the revolution
section to revolve with respect to the subject; an X-ray radiation
area setting section that accepts a setting of a local area of the
subject as an X-ray radiation area; and a control section that
controls at least the revolution driving section; wherein the
revolution section is revolved with respect to the X-ray radiation
area to perform CT imaging; and wherein the X-ray CT imaging method
comprising the step of, when a high sensitivity site of a
biological body that is highly sensitive to an X-ray is located in
an area where an X-ray flux in a revolving movement passes during
the CT imaging in accordance with the X-ray radiation area accepted
by the X-ray radiation area setting section, controlling at least
one of an X-ray revolution plane formed by the X-ray flux along
with the revolution of the revolution section and a revolution
range of the revolution section, such that an amount of X-ray
radiation toward the high sensitivity site is decreased in
accordance with the X-ray radiation area accepted by the X-ray
radiation area setting section, the control being performed by the
control section.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
The present application claims benefit of priority under 35 U.S.C.
.sctn.119 to Japanese Patent Application No. 2013-046862 filed on
Mar. 8, 2013. The contents of the priority applications are
incorporated by reference in their entirety.
BACKGROUND OF THE INVENTION
1. Field of the Invention
The present invention relates to an X-ray CT imaging device and an
X-ray imaging method for performing CT imaging by detecting, by an
X-ray detector, an X-ray directed from an X-ray generator toward a
subject located between the X-ray generator and the X-ray
detector.
2. Description of the Prior Art
Conventionally, in the fields of medical care and the like, CT
(computerized tomography) imaging is performed. According to the CT
imaging, an X-ray beam is directed toward a subject to collect
projection data, and the obtained projection data is re-constructed
on a computer to generate a CT image (volume rendering image,
etc.).
CT imaging is performed as follows. A subject is located between an
X-ray generator and an X-ray detector. While the X-ray generator
and the X-ray detector are revolved around the subject, a cone-like
X-ray beam (X-ray cone beam) is directed toward the subject from
the X-ray generator. The results of the X-ray detection (projection
data) are collected by the X-ray detector, and three-dimensional
data is re-constructed based on the collected X-ray detection
results. A device usable for performing such CT imaging is
disclosed in, for example, Patent Document 1.
According to Patent Document 1, the CT imaging device described
therein operates as follows. During CT imaging, a pair of channel
collimators are displaced in front of the X-ray generator such that
a CT imaging area (field of view (FOV)), namely, an area irradiated
with an X-ray (hereinafter, referred as the "X-ray radiation
area"), becomes circular or elliptical. Thus, CT imaging can be
performed only on an area of interest of a patient, who is a
subject of the CT imaging.
However, there is a case where the area passed by an X-ray cone
beam generated by the X-ray detector and revolving, namely, a flux
of X-rays revolving during the CT imaging, encompasses a high
sensitivity site of a biological body that is sensitive to X-rays
such as, for example, submandibular gland, parotid gland,
sublingual gland, thyroid gland, or lens of the eyeball. In such a
case, especially when the patient has abnormality in such a high
sensitivity site, the X-ray flux passing the high sensitivity site
exerts a large influence. Therefore, care should be taken when the
CT imaging is performed.
PRIOR ART DOCUMENT
Patent Document
Patent Document 1: Japanese Laid-Open Patent Publication No. Hei
11-19078
SUMMARY OF THE INVENTION
One or more embodiments of the present invention provide an X-ray
CT imaging device and an X-ray CT imaging method capable of, even
when a high sensitivity site is in the vicinity of an X-ray
radiation area that is set for an imaging target site, performing
CT imaging on the imaging target site while keeping the exposure
dose of the high sensitivity site low.
One or more embodiments of the present invention are directed to an
X-ray CT imaging device including a revolution section that causes
an X-ray generation source and an electric X-ray detector, facing
each other while having a subject therebetween, to revolve about a
revolution shaft as a center of revolution; a revolution driving
section that drives driving the revolution section to revolve with
respect to the subject; an X-ray radiation area setting section
that accepts a setting of a local area of the subject as an X-ray
radiation area; a control section that controls at least the
revolution driving section; and a high sensitivity site
specification section to specify a high sensitivity site in a
biological body that is highly sensitive to an X-ray. The
revolution section is revolved with respect to the X-ray radiation
area to perform CT imaging. When radiation of an X-ray flux in a
revolving movement is performed during the CT imaging in accordance
with the X-ray radiation area accepted by the X-ray radiation area
setting section, the control section controls at least one of an
X-ray revolution plane formed by the X-ray flux along with the
revolution of the revolution section, and a revolution range of the
revolution section, such that an amount of X-ray radiation toward
the high sensitivity site is decreased.
The "X-ray CT imaging device" encompasses an imaging device capable
of performing CT imaging with the imaging revolution range of about
180 degrees and about 360 degrees, and an imaging device capable of
performing DVT imaging or tomosynthesis imaging with no limitation
on the imaging revolution range.
The "revolution driving section that drives the revolution section
to revolve with respect to the subject" drives the revolution
section to perform horizontal evolution, to perform inclination
revolution in which the revolution section is inclined, to move
upward and downward and then perform horizontal revolution, and to
revolve after the subject is moved upward and downward.
The "high sensitivity site" encompasses a high sensitivity site set
at a position by an operation made by an operator and a high
sensitivity site selected automatically or semi-automatically from
high sensitivity sites at preset positions.
Owing to this, even when a high sensitivity site is in the vicinity
of the X-ray radiation area that is set for an imaging target site,
CT imaging can be performed on the imaging target site with
certainty while keeping the exposure dose of the high sensitivity
site low.
This will be described in more detail. The control section controls
at least one of the X-ray revolution plane formed by the X-ray flux
along with the revolution of the revolution section and the
revolution range of the revolution section in order to decrease the
X-ray radiation to the high sensitivity site specified by the high
sensitivity site specification section when the X-ray radiation is
performed toward the X-ray irradiation area accepted by the X-ray
radiation area setting section.
In one or more embodiments of the present invention, the high
sensitivity site specification section may specify the high
sensitivity site in a schematic view of a head of the subject.
The "high sensitivity site specification section to specify the
high sensitivity site" encompasses a specification section to
specify a high sensitivity site automatically, semi-automatically,
by a selection operation made by an operator or by any other
operation, from a plurality of registered high sensitivity sites,
based on information on the high sensitivity sites such as the
position, size, sensitivity or the like, and also encompasses other
specification sections to specify information on the high
sensitivity sites by various methods.
Owing to this, even when a high sensitivity site is in the vicinity
of the X-ray radiation area that is set for an imaging target site,
CT imaging can be performed on the imaging target site with
certainty while keeping the exposure dose of the high sensitivity
site low.
This will be described in more detail. The control section controls
at least one of the X-ray revolution plane formed by the X-ray flux
along with the revolution of the revolution section and the
revolution range of the revolution section in order to decrease the
X-ray radiation to the high sensitivity site specified by the high
sensitivity site specification section when the X-ray radiation is
performed toward the X-ray irradiation area accepted by the X-ray
radiation area setting section. Therefore, even when a high
sensitivity site specified by the high sensitivity site
specification section is in the vicinity of the X-ray radiation
area that is set for an imaging target site, CT imaging can be
performed on the imaging target site with certainty while keeping
the exposure dose of the high sensitivity site low.
In one or more embodiments of the present invention, the control
section may perform revolution range control of changing at least
one of an X-ray radiation start position and an X-ray radiation end
position in the revolution range in accordance with the X-ray
radiation area set by the X-ray radiation area setting section and
the high sensitivity site.
Owing to this, the revolution range of the revolution section can
be adjusted without changing the X-ray revolution plane of the
revolution section. Therefore, the exposure dose of the high
sensitivity site can be easily decreased.
In one or more embodiments of the present invention, the control
section may perform control of changing at least one of an X-ray
radiation angle with respect to a predetermined reference plane and
a radiation position on the subject to control the x-ray revolution
plane in accordance with the X-ray radiation area set by the X-ray
radiation area setting section and the high sensitivity site.
The "determined reference plane" is a generally horizontal plane
when the subject is standing up or sitting down, and is a generally
vertical plane when the subject is lying down.
The "radiation position" on the subject may be a position in a
direction intersecting the reference plane on which the revolution
section revolves, for example, a position in a height direction
when the revolution section revolves in the horizontal
direction.
Owing to this, at least one of the X-ray radiation angle with
respect to the determined reference plane and the radiation
position on the subject is changed, so that the CT imaging can be
performed on the imaging target site in the set X-ray radiation
area with certainty while the exposure dose of the high sensitivity
site in the vicinity of the X-ray radiation area is decreased.
In one or more embodiments of the present invention, the X-ray CT
imaging device may further include a support section that supports
the revolution section via the revolution shaft; and a support
section moving section that moves the support section. The support
section moving section may include at least one of a shaft moving
mechanism that moves the revolution shaft with respect to the
support section and a relative moving mechanism that moves the
support section with respect to the subject. The control section
may control the movement of the support section moving section thus
to control the X-ray revolution plane.
Owing to this, the support section that supports the revolution
section via the revolution shaft can be moved by the support
section moving section. Therefore, the exposure dose of the high
sensitivity site can be easily decreased.
In one or more embodiments of the present invention, the X-ray CT
imaging device may further include an X-ray radiation range
restriction section that restricts an X-ray radiation range, the
X-ray radiation range restriction section being provided forward to
the X-ray generation source in an X-ray radiation direction. The
control section may control the restriction of the X-ray radiation
range restriction section thus to control the X-ray revolution
plane.
Owing to this, the X-ray radiation range restricted by the X-ray
radiation range restriction section can be changed. Therefore, the
exposure dose of the high sensitivity site can be easily
decreased.
In one or more embodiments of the present invention, the X-ray CT
imaging device may further include a control pattern storage
section that stores a control pattern by the control section for
each of set areas that are each set as the X-ray radiation area by
the X-ray radiation area setting section.
Owing to this, the CT imaging can be performed in such a manner
that the exposure dose of the high sensitivity site is decreased by
merely setting the X-ray radiation area by use of the X-ray
radiation area setting section.
In one or more embodiments of the present invention, the X-ray CT
imaging device may further include a high sensitivity site
information storage section that stores information on the high
sensitivity site.
Owing to this, information on the high sensitivity site such as,
for example, the position, size, sensitivity degree, priority level
(weighting degree) or the like stored on the high sensitivity site
information storage section can be retrieved. Thus, the CT imaging
can be performed in such a manner that the exposure dose of the
high sensitivity is decreased.
In one or more embodiments of the present invention, the X-ray
radiation area setting section may display an image containing the
X-ray radiation area and accept a setting that sets the X-ray
radiation area with respect to the displayed image, and may also
display the high sensitivity site as overlapping the image.
The image may be a scout image, a panorama image, a cephalo image,
a schematic illustration or an optically captured photo of the
subject, or a combination thereof.
Owing to this, the high sensitivity site displayed as overlapping
the image which encompasses the X-ray radiation area can be
visually checked. Therefore, the high sensitivity site, the
exposure dose of which is to be decreased during the CT imaging,
can be specified with more certainty.
In one or more embodiments of the present invention, the X-ray CT
imaging device may further include a high sensitivity site
replacing section that replaces the high sensitivity site displayed
as overlapping the image with another high sensitivity site.
The "high sensitivity site replacing section that replaces the high
sensitivity site" may be a replacing section that replaces at least
a display or parameter of any of various types of detailed
information such as the size, position, sensitivity, priority level
(weighting degree) and the like.
Owing to this, the CT imaging can be performed in an appropriate
manner in accordance with the situation of the subject. For
example, a higher priority level is assigned to a high sensitivity
site which is far from the set X-ray radiation area but has
abnormality occurring, instead of a high sensitivity site closest
to the set X-ray radiation area.
In one or more embodiments of the present invention, the X-ray CT
imaging device may further include an X-ray imaging preparation
switch that revolves the revolution section to the X-ray radiation
start position in the revolution range in accordance with the set
area that is set by the X-ray radiation area setting section, the
revolution range being different for each of the set areas; and an
X-ray radiation switch that directs the X-ray toward the set area
while revolving the revolution section to perform imaging.
Owing to this, for example, the revolution section is revolved to
the start position of the X-ray radiation range to prepare for
imaging, and the revolution section is further revolved by the
X-ray radiation switch. Thus, CT imaging can be performed in such a
manner that the exposure dose of the high sensitivity site is
decreased.
In one or more embodiments of the present invention, the X-ray CT
imaging device may further include a movement driving section that
moves the revolution section. The control section may perform
driving control that moves the revolution section with respect to
the movement driving section. In the driving control, controls for
both of the revolution of the revolution section and the movement
of the revolution section caused by moving the revolution shaft by
the movement driving section may be performed concurrently to allow
panorama X-ray imaging to be performed.
Owing to this, when a panorama image is needed, panorama X-ray
imaging can be performed with no need to prepare another X-ray
imaging device.
In one or more embodiments of the present invention, the X-ray CT
imaging device may further include a cephalo-imaging head fixation
device provided perpendicularly to a direction of the revolution
shaft, and thus cephalo-X-ray imaging may be allowed to be
performed.
Owing to this, when a cephalogram is needed, cephalo X-ray imaging
can be performed with no need to prepare another X-ray imaging
device.
One or more embodiments of the present invention are also directed
to an X-ray CT imaging method performed by use of an X-ray CT
imaging device. The X-ray CT imaging device includes a revolution
section that causes an X-ray generation source and an electric
X-ray detector, facing each other while having a subject
therebetween, to revolve about a revolution shaft as a center of
revolution; a revolution driving section that drives the revolution
section to revolve with respect to the subject; an X-ray radiation
area setting section that accepts a setting of a local area of the
subject as an X-ray radiation area; and a control section that
controls at least the revolution driving section. The revolution
section is revolved with respect to the X-ray radiation area to
perform CT imaging. The X-ray CT imaging method includes the step
of, when a high sensitivity site of a biological body that is
highly sensitive to an X-ray is located in an area where an X-ray
flux in a revolving movement passes during the CT imaging in
accordance with the X-ray radiation area accepted by the X-ray
radiation area setting section, controlling at least one of an
X-ray revolution plane formed by the X-ray flux along with the
revolution of the revolution section and a revolution range of the
revolution section, such that an amount of X-ray radiation toward
the high sensitivity site is decreased in accordance with the X-ray
radiation area accepted by the X-ray radiation area setting
section, the control being performed by the control section.
Owing to this, even when a high sensitivity site is in the vicinity
of the X-ray radiation area that is set for an imaging target site,
CT imaging can be performed on the imaging target site with
certainty while keeping the exposure dose of the high sensitivity
site low.
One or more embodiments of the present invention provide an X-ray
CT imaging device and an X-ray CT imaging method capable of, even
when a high sensitivity site is in the vicinity of an X-ray
radiation area that is set for an imaging target site, performing
CT imaging on the imaging target site while keeping the exposure
dose of the high sensitivity site low.
BRIEF DESCRIPTION OF DRAWINGS
FIG. 1 is a schematic isometric view of an X-ray imaging
device.
FIG. 2 is a partial front view of the X-ray imaging device in the
state of including a cephalostat.
FIG. 3 is a block diagram showing a structure of the X-ray imaging
device.
FIG. 4 is a schematic isometric view of a beam formation
mechanism.
FIG. 5 is a schematic view showing a setting screen to set an
imaging target site as a CT imaging area.
FIG. 6 is a schematic view of a setting screen to set a high
sensitivity site.
FIG. 7 is a flowchart showing a CT imaging process.
FIG. 8 is a schematic side view showing CT imaging performed on the
upper jaw.
FIG. 9 is a schematic side view showing CT imaging performed on the
lower jaw.
FIG. 10 is a schematic plan view showing common CT imaging
performed with an X-ray cone beam revolving in a revolution range
of 180 degrees.
FIG. 11 is a schematic plan view showing exposure dose-suppressed
CT imaging performed with the revolution range of the X-ray cone
beam being controlled.
FIG. 12 is a schematic plan view of the X-ray cone beam.
FIG. 13 is a schematic plan view showing a trajectory of the X-ray
cone beam revolving in the revolution range of 180 degrees.
FIG. 14 is a schematic side view showing exposure dose-suppressed
CT imaging performed on the upper jaw set as an imaging site, the
CT imaging being performed by controlling the height and the
radiation angle of the X-ray cone beam.
FIG. 15 is a schematic side view showing exposure dose-suppressed
CT imaging performed on the lower jaw set as an imaging site, the
CT imaging being performed by controlling the height and the
radiation angle of the X-ray cone beam.
FIG. 16 is a schematic view showing exposure dose-suppressed CT
imaging performed on the thyroid gland.
FIG. 17 shows exposure dose-suppressed CT imaging performed on the
lens of the eyeball.
FIG. 18 is a flowchart showing exposure dose-suppressed CT imaging
performed with the revolution range of the X-ray cone beam being
controlled in the case where there are a plurality of high
sensitivity sites.
FIG. 19 is a schematic plan view showing exposure dose-suppressed
CT imaging performed with the revolution range of the X-ray cone
beam being controlled in the case where there are a plurality of
high sensitivity sites.
FIG. 20 is a flowchart showing exposure dose-suppressed CT imaging
performed with the height and the radiation angle of the X-ray cone
beam being controlled in the case where there are a plurality of
high sensitivity sites.
FIG. 21 is a schematic side view showing exposure dose-suppressed
CT imaging performed with the height and the radiation angle of the
X-ray cone beam being controlled in the case where there are a
plurality of high sensitivity sites.
FIG. 22 shows exposure dose-suppressed CT imaging performed with
the height and the radiation angle of the X-ray cone beam being
controlled in the case where there are a plurality of high
sensitivity sites.
FIG. 23 is a schematic view of another type of X-ray imaging
device.
FIG. 24 is a schematic side view of the X-ray imaging device shown
in FIG. 23.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
Hereinafter, an X-ray CT imaging device and an X-ray CT imaging
method according to one or more embodiments of the present
invention will be described with reference to FIG. 1 through FIG.
17.
FIG. 1 is a schematic isometric view of an X-ray imaging device 1.
FIG. 2 is a partial front view of the X-ray imaging device in the
state of including a cephalostat 43. FIG. 3 is a block diagram
showing a structure of the X-ray imaging device 1. FIG. 4 is a
schematic isometric view of a beam formation mechanism 13. FIG. 5
is a schematic view of an imaging area setting screen 600 to set an
imaging target site OB as a CT imaging area CA. In FIG. 5, the
X-ray imaging device 1 is used for dental care, and the imaging
target site OB includes the jaw bones. FIG. 6 is a schematic view
of a high sensitivity site specification screen 700 to set a high
sensitivity site H.
FIG. 7 is a flowchart showing a CT imaging process. FIG. 8 is a
schematic side view showing CT imaging performed on the upper jaw.
FIG. 9 is a schematic side view showing CT imaging performed on the
lower jaw. FIG. 10 is a schematic plan view showing common CT
imaging performed with an X-ray cone beam revolving in a revolution
range of 180 degrees. FIG. 11 is a schematic plan view showing
exposure dose-suppressed CT imaging performed with the revolution
range of the X-ray cone beam being controlled. FIG. 12 is a
schematic plan view of the X-ray cone beam. FIG. 13 is a schematic
plan view showing a trajectory of the X-ray cone beam revolving in
the revolution range of 180 degrees.
FIG. 14 is a schematic side view showing exposure dose-suppressed
CT imaging performed on the upper jaw set as an imaging site, the
CT imaging being performed by controlling the height and the
radiation angle of the X-ray cone beam. In this specification, the
"height" refers to the level of an element in the Z-axis direction
except for the body height of a subject M1 mentioned below. FIG. 15
is a schematic side view showing exposure dose-suppressed CT
imaging performed on the lower jaw set as an imaging site, the CT
imaging being performed by controlling the height and the radiation
angle of the X-ray cone beam. FIG. 16 is a schematic view showing
exposure dose-suppressed CT imaging performed on the thyroid gland.
FIG. 17 shows exposure dose-suppressed CT imaging performed on the
lens of the eyeball. FIG. 18 and the other figures will be
specifically described later.
The X-ray imaging device 1 includes a main body part 2 that
performs CT imaging to collect projection data and an information
processing device 8 that processes the projection data collected by
the main body part 2 to generate various types of images. The main
body part 2 is preferably accommodated in a hollow parallelepiped
X-ray-proof chamber 70, and is connected, via a connection table
83, to the information processing device 8 located outside the
X-ray-proof chamber 70.
The main body part 2 includes an X-ray generation section 10 that
emits an X-ray cone beam Bx formed of a flux of X-rays toward the
subject M1 or an X-ray slit beam, an X-ray detection section
detector 20 including an X-ray detector 20a that detects the X-ray
cone beam Bx or an X-ray slit beam emitted by the X-ray generation
section 10, a revolving arm 30 that supports the X-ray generation
section 10 and the X-ray detection section 20, a support pillar 50
extending in a vertical direction, a revolving arm elevation
section 40 which suspends the revolving arm 30 and is movable
upward and downward in the vertical direction with respect to the
support pillar 50, and a main body control section 60. The X-ray
generation section 10, the X-ray detection section 20, and a beam
formation mechanism 13 provided in the X-ray generation section 10
on the side facing the X-ray detection section 20 are included in
an imaging mechanism 3.
The X-ray generation section 10 and the X-ray detection section 20
are suspended from, and fixed at, both of two ends of the revolving
arm 30 respectively, and are supported so as to face each other.
The revolving arm 30 is suspended from, and fixed to, the revolving
arm elevation section 40 via a revolution shaft 31 extending in the
vertical direction.
The revolving arm 30 is inverted U-shaped as seen in a front view
and is revolvable about the revolution shaft 31 provided at a top
end thereof. The revolution shaft 31 acts as a revolution center
Sc. The X-ray generation section 10 and the X-ray detection section
20 are respectively attached to both of the two ends of the
revolving arm 30. The revolving arm 30 is equipped with an X-ray
detection section driving section 23 that moves the X-ray detection
section 20, more specifically, the X-ray detector 20a, with respect
to the revolving arm 30.
The X-ray detection section driving section 23 that moves the X-ray
detection section 20, more specifically, the X-ray detector 20a,
with respect to the revolving arm 30, may be any of various types
of actuators, although not shown.
The X-ray detector 20a may be moved with respect to the revolving
arm 30 as follows. For example, the X-ray detection section driving
section 23 includes a roller fixed to a shaft of a motor which is
fixed to a base part of the X-ray detection section driving section
23. Separately, a member that guides the X-ray detector 20a in a
Z-axis direction is provided. The roller is put into contact with a
rear surface of the X-ray detector 20a to move the X-ray detector
20a upward and downward via the member.
Alternatively, the X-ray detection section driving section 23
includes a male screw part pivotably fixed to the base part of the
X-ray detection section driving section 23. Separately, a member
that guides the X-ray detector 20a in the Z-axis direction and a
female screw part fixed to the rear surface of the X-ray detector
20a are provided. The female screw part is moved upward and
downward by the male screw part via the member to move the X-ray
detector 20a upward and downward in the Z-axis direction using a
motor as a driving source.
The revolving arm 30 is not limited to having the above-described
shape. For example, the revolving arm 30 may include an annular
part and rotate about the center thereof, and the X-ray generation
section 10 and the X-ray detection section 20 may be supported by
the revolving arm 30 so as to face each other.
Hereinafter, a direction parallel to an axial direction of the
revolving shaft 31 (herein, the vertical direction) is defined as
the "Z-axis direction", and a direction intersecting the Z-axis
direction is defined as an "X-axis direction". A direction
intersecting the X-axis direction and the Z-axis direction is
defined as a "Y-axis direction". The X-axis direction and the
Y-axis direction may be defined arbitrarily. Herein, where a test
subject, namely, the subject M1, stands facing the support pillar
50 in the X-ray CT imaging device 1, the left-right direction for
the subject M1 is defined as the "X-axis direction", and the
front-rear direction for the subject M1 is defined as the "Y-axis
direction". In this embodiment, the X-axis direction, the Y-axis
direction and the Z-axis direction are perpendicular to each other.
Hereinafter, the Z-axis direction may be referred to as the
"vertical direction", and a direction in a plane defined by the
X-axis direction and the Y-axis direction may be referred to as a
"horizontal direction".
Regarding the X-axis direction, a rightward direction for the test
subject is defined as a (+X) direction. Regarding the Y-axis
direction, a rearward direction for the test subject is defined as
a (+Y) direction. Regarding the Z-axis direction, the vertically
upward direction for the test subject is defined as a (+Z)
direction.
Regarding a three-dimensional coordinate system for the revolving
arm 30, a direction in which the X-ray generation section 10 and
the X-ray detection section 20 face each other is defined as a
"y-axis direction", a horizontal direction perpendicular to the
y-axis direction is defined as an "x-axis direction". A vertical
direction perpendicular to the x-axis direction and the y-axis
direction is defined as a "z-axis direction". In this embodiment,
the Z-axis direction is the same as the z-axis direction. In this
embodiment, the revolving arm 30 revolves about the revolution
shaft 31, extending in the vertical direction, as the revolution
axis. Therefore, the xyz Cartesian coordinate system rotates about
the Z-axis (=z-axis) with respect to the XYZ Cartesian coordinate
system.
Where the X-ray generation section 10 and the X-ray detection
section 20 shown in FIG. 1 are seen in a plan view, a direction
from the X-ray generation section 10 to the X-ray detection section
20 is defined as a "(+y) direction". A horizontal rightward
direction perpendicular to the (+y) direction is defined as a "(+x)
direction", and an upward direction in the vertical direction is
defined as a "(+z) direction".
In the following description, an operation made by an operator may
be occasionally included in a process of actuation of the device.
This is based on the premise that an operation section of the
device accepts an operation made by the operator.
The revolving arm elevation section 40 includes a top frame 41 and
a bottom frame 42, and protrudes in a direction opposite to the
side engageable with the support pillar 50 standing in the vertical
direction, namely, protrudes in a front direction.
The top frame 41 includes a revolution shaft 31 to which the
revolving arm 30 is attached, and a built-in elevation section 41a.
The revolution shaft 31 attached to the revolving arm 30 is
attached to the elevation section 41a. The elevation section 41a is
movable in the vertical direction along the support pillar 50.
Thus, the top frame 41 can move the revolving arm 30 upward and
downward with respect to the support pillar 50.
The top frame 41 includes a revolution driving section 30s and a
revolution shaft moving section 30m. The revolution driving section
30s includes a revolving motor (not shown) that revolves the
revolving arm 30 about the revolution shaft 31 and a transmission
mechanism (not shown) including a belt, a pulley, a rotation shaft
and the like and passes the revolution shaft 31. The revolution
driving section 30s transmits a rotation force of the revolving
motor to the revolving arm 30 by the transmission mechanism to
revolve the revolving arm 30. The revolution shaft moving section
30m moves the revolution shaft 31 in the x-axis direction and the
y-axis direction with respect to the top frame 41.
The revolution shaft 31 and the revolving arm 30 have a bearing
(not shown) therebetween so that the revolving arm 30 revolves
smoothly about the revolution shaft 31.
The revolution shaft moving section 30m moves the revolution shaft
31 in the x-axis direction and the y-axis direction and thus can
move the revolution center Sc. Therefore, the revolution shaft
moving section 30m also acts as a revolution center moving
section.
As disclosed in Japanese Laid-Open Patent Publication No.
2007-29168 and WO2009/063974 filed by the Applicant of the present
application, the revolution shaft moving section 30m may be used to
locate the revolution center Sc of the revolving arm 30 at a
position different from the position of the center of the
revolution shaft 31, which is a mechanical member that axially
revolves the revolving arm 30. In this case, the revolution center
Sc may be displaced in the x-axis direction and the y-axis
direction.
In the example shown in the figures, the top frame 41 includes
mechanical elements that drives the revolving arm 30, and acts as a
revolving arm driving section 30K. The top frame 41 acting as the
revolving arm driving section 30K drives the revolving arm 30 to
drive the imaging mechanism 3, and thus also acts as an imaging
mechanism driving section.
The revolving motor may be fixed inside the top frame 41, but
alternatively may be fixed inside the revolving arm 30 so that a
pivoting force acts on the revolution shaft 31. In this embodiment,
the revolution shaft 31 extends in the vertical direction.
Alternatively, the revolution shaft 31 may be inclined with respect
to the vertical direction at an angle in a range including 90
degrees. Namely, the revolution shaft 31 may be perpendicular to
the vertical direction.
In this embodiment, the revolution driving section 30s that
revolves the revolving arm 30 includes the revolution shaft 31, the
transmission mechanism including the bearing, the belt, the
rotation shaft and the like, and the revolving motor, and revolves
the revolving arm 30 about the revolution shaft 31, which is not
rotated. The structure of revolving the revolving arm 30 is not
limited to this.
For example, the revolution shaft 31 rotatably fixed to the
revolving arm 30 may be rotated with respect to the top frame 41 so
that the revolving arm 30 is revolved.
The bottom frame 42 is equipped with a subject holding section 421
including a head holder that fixes the subject M1 (in this example,
the head of a human body) from left and right, a chin rest that
fixes the chin or the like, and is also equipped with a subject
holding section driving section 422 that moves the subject holding
section 421. An ear rod including a part insertable into left and
right earholes of the head of a human body may be used as the
subject holding section 421.
In the case where the subject holding section 421 is a chin rest,
the subject holding section driving section 422 may be, for
example, an elevation actuator (not shown) that moves the chin rest
upward and downward with respect to the bottom frame 42.
The elevation actuator that moves the chin rest upward and downward
may have, for example, the following structure.
A screw shaft and a position adjusting motor similar to a length
direction screw shaft 161a and a length direction position
adjusting motor 162a described later with reference to FIG. 4 are
fixed to the bottom frame 42. A screw groove similar to a screw
groove 141 shown in FIG. 4 is fixed to the chin rest. The position
adjusting motor is driven to rotate the screw shaft forward and
rearward. As a result, the screw groove moves upward and downward
in a length direction to move the chin rest upward and
downward.
In the case where the CT imaging area CA has a width in the up-down
direction that is equal to, or less than, the height of the teeth
in the upper jaw or the teeth in the lower jaw, the elevation
actuator is actuated to move the head of the subject M1 in
accordance with whether the X-ray imaging target is the teeth in
the upper jaw or the teeth in the lower jaw, so that the target
site is encompassed in the CT imaging area CA.
In the case where the subject holding section 421 is a chair on
which the subject M1 sits, the subject holding section driving
section 422 may be, for example, an elevation actuator (not shown)
that moves the chair upward and downward. Such an elevation
actuator may be a larger version of the actuator that moves the
chin rest upward and downward.
The elevation actuator is not limited to moving the chair in the
Z-axis direction, but may move the chair in the X-axis direction or
in the Y-axis direction by use of a known XY table or the like.
The revolving arm 30 is moved upward or downward by the revolving
arm elevation section 40 in accordance with the body height of the
subject M1 and is located at an appropriate position. In this
state, the subject M1 is held by the subject holding section 421.
In the example shown in FIG. 1, the subject holding section 421
holds the subject M1 such that the body axis of the subject M1 is
in substantially the same direction as that of the axial direction
of the revolution axis 31.
In the X-ray imaging device 1, one of the elevation section 41a and
the subject holding section driving section 422 (especially, the
mechanical element that moves the subject M1 upward and downward)
may be omitted. Alternatively, both of the elevation section 41a
and the subject holding section driving section 422 may be omitted.
In this case, the top frame 41 or the subject holding section 421
is moved upward and downward manually.
The main body control section 60 controls the operation of each
element of the main body part 2. As shown in FIG. 3, the main body
control section 60 is located inside the main body part 2.
In more detail, the main body control section 60 is connected to
the X-ray generation section 10, the X-ray detection section
driving section 23, the revolving arm driving section 30K, the
subject holding section driving section 422, an X-ray radiation
range restriction section driving section 16, a display section 61,
an operation panel 62 acting as an operation section, a
communication interface 63 (hereinafter, referred to as the
"communication I/F 63"), and a storage section 64. The main body
control section 60 communicates with, and thus controls, each of
these elements. The X-ray radiation range restriction section
driving section 16, the surface section 61, the operation panel 62
acting as the operation section, the communication interface 63,
and the storage section 64 will be described later.
The display section 61 may include a touch panel or the like so as
to include apart of, or the entirety of, the functions of the
operation section 62. In this case, the display section 61 also
acts as the operation section 62.
The operation panel 62 is connected to an operation switch section
65. The operation switch section 65 includes a standby switch 65a,
which is an operation switch that moves the revolving arm 30 to a
revolution start position Ls when being pressed before start of CT
imaging, and an imaging actuation switch 65b, which is an operation
switch that directs the X-ray cone beam Bx toward the X-ray
detection section 20 from the X-ray generation section 10 and
revolving the revolving arm 30 to perform the CT imaging when being
kept pressed.
The imaging actuation switch 65b may be a well-known switch
conventionally referred to as a "dead man's switch". Alternatively,
the imaging actuation switch 65b may also have a function of the
standby switch 65a. In this case, the imaging actuation switch 65b
moves the revolving arm 30 to the revolution start position Ls when
being turned on for the first time, and keeps directing the X-ray
beam Bx when being turned on for the second time (while being kept
pressed).
The communication I/F 63 is connected to a connection cable 83 of
an information processing main body part 80 to communicate with the
information processing main body part 80. The storage section 64
stores, for example, information on the high sensitivity site H
described later, and a control program usable by the main body
control section 60 that controls each of the elements.
A default high sensitivity site H may be registered in terms of the
position or range, or may be set to be registered or deleted by the
operator. Alternatively, a default high sensitivity site H may be
registered, and another high sensitivity site H may be newly
registered or deleted by the operator. The portion that accepts a
specification on a high sensitivity site H that includes the high
sensitivity site specification section 700 is an example of high
sensitivity site specification section. In the case where a default
high sensitivity site H is registered, the portion that accepts the
registration of the position and range thereof is another example
of high sensitivity site specification section. The portion that
stores the position and range of the registered high sensitivity
site H is an element of the high sensitivity site specification
section. In the structure that allows the operator to specify a
high sensitivity site H each time, any site can be specified as the
high sensitivity site H. In the structure that allows a default
high sensitivity site H to be registered, the operator does not
need to make a specification operation. Each structure has its own
advantage.
The main body control section 60 connected to the elements
described above uses the control program stored on the storage
section 64 to act as a mode setting section 60a, a revolving arm
trajectory setting section 60b and a revolving arm driving control
section 60c that controls the revolving arm driving section 30K, an
X-ray detection section driving control section 60d that controls
the driving of the X-ray detection section driving section 23, a
subject holding section driving control section 60e that controls
the driving of the subject holding section driving section 422, an
X-ray radiation range restriction section driving control section
60f that controls the driving of the X-ray radiation range
restriction section driving section 16, or an X-ray generation
section driving control section 60g that controls the driving of
the X-ray generation section 10.
The revolving arm driving control section 60c controls a revolution
range L of the revolving arm 30, and also performs control on the
height of the revolving arm 30 and the setting of an X-ray
revolution plane described later. The X-ray detection section
driving control section 60d controls the height of the X-ray
detection section by use of the X-ray detection section driving
section 23 to perform control on the setting of the X-ray
revolution plane and thus to perform control on the imaging of the
X-ray detector 20a.
The X-ray radiation range restriction section driving control
section 60f controls the height of an opening 17 of the beam
formation mechanism 13 described later by use of the X-ray
radiation range restriction section driving section 16 to perform
control on the setting of the X-ray revolution plane. The X-ray
generation section driving control section 60g controls the X-ray
generation performed by an X-ray generator 10a included in the
X-ray generation section 10.
The X-ray cone beam Bx is revolved while radiating, and therefore,
forms a planar revolution trajectory having a certain thickness
along with the revolution. A plane formed by such a revolution
trajectory will be referred to as the "revolution plane".
The display section 61 including a liquid crystal monitor or the
like that displays various types of information based on the
control performed by the main body control section 60, and the
operation panel 62 including buttons or the like that inputs
various types of instructions to the main body control section 60,
are attached to an outer wall of the X-ray-proof chamber 70 that
accommodates the main body part 2.
The operation panel 62 has a function of an X-ray radiation range
specification section 62a to specify the position or the like of an
imaging area encompassing an imaging target site, namely, a CT
imaging area CA, when displaying the imaging area setting screen
600 described later, and also has a function of a high sensitivity
site setting section 62b to set a high sensitivity site H when
displaying the high sensitivity site specification screen 700. The
operation panel 62 is also usable for, for example, specifying the
imaging area or the high sensitivity site H. The X-ray imaging may
be performed in various modes. The operation panel 62 may be
operated to select a mode.
The operation panel 62 may be provided in the main body part 2, or
provided outside the outer wall of the X-ray-proof chamber 70 and
also in the main body part 2.
The information processing device 8 includes the information
processing main body part 80, a display section 81 including a
display device such as, for example, a liquid crystal monitor, an
operation section 82 including a keyboard, a mouse and the like, a
control section 84, a storage section 85 that stores a control
program usable by the control section 84 that controls each of the
elements, a computation section 86, and a communication I/F 87.
The display section 81, the operation section 82, the storage
section 85 and the computation section 86 are connected to the
control section 84. The control section 84 uses the control program
stored on the storage section 85 to control each of the elements.
The computation section 86 uses an image processing program stored
on the storage section 85 to act as an image processing section
86a.
An operator can input any of various instructions to the
information processing device 8 having the above-described
structure via the operation section 82. The display section 81 may
include a touch panel. In this case, the display section 81 has a
part of, or the entirety of, the functions of the operation section
82 and also acts as the operation section 82.
The display section 81 may display an image of various buttons or
the like so that the buttons can be turned ON by an operation made
on a pointer by a mouse or the like. In this case also, the display
section 81 also acts as the operation section 82.
The information processing device 80 may be, for example, a
computer, a work station or the like, and can transmit and receive
various types of data with the main body part 2 via the
communication I/F 87 by the connection cable 83, which is a
communication cable. The communication between the main body part 2
and the information processing device 8 may be performed
wirelessly.
The information processing device 8 processes projection data
acquired by the main body part 2 by use of the image processing
section 86a of the computation section 86 to re-construct
three-dimensional data (volume data) represented by voxels. For
example, the information processing device 8 can set a specific
plane in the three-dimensional data, and re-construct a tomographic
image of the specific plane.
Now, with reference to FIG. 4, the beam formation mechanism 13
provided in the X-ray generation section 10 will be described. The
beam formation mechanism 13 partially blocks the X-ray generated by
the X-ray generator 10a to restrict a radiation range thereof, such
that the X-ray cone beam Bx directed toward the X-ray detection
section 20 has a conical shape. In this specification, the term
"conical shape" encompasses the conical shape in the generally used
sense and also a pyramid shape.
The X-ray generation section 10 suspended from the revolving arm 30
so as to face the X-ray detection section 20 includes the X-ray
generator 10a accommodated in a housing 11, and the X-ray generator
10a includes an X-ray tube. In a front surface of the housing 11,
an output opening 12 that transmits the X-ray generated in the
X-ray generator 10a accommodated in the housing 11 is formed.
Forward to the output opening 12 (toward the viewer of FIG. 4, and
in the y-axis direction from the X-ray generation section 10, more
specifically, in the +y direction from the X-ray generation section
10), the beam formation mechanism 13 is provided.
The beam formation mechanism 13 includes length direction X-ray
radiation restriction sections 14 (14a, 14b) that block the X-ray
in a length direction of the radiation range (z-axis direction),
lateral direction X-ray radiation restriction sections 15 (15a,
15b) that block the X-ray in a lateral direction of the radiation
range (x-axis direction), and the X-ray radiation range restriction
section driving section 16 (16a and 16b) that moves the length
direction X-ray radiation restriction sections 14 and the lateral
direction X-ray radiation restriction sections 15.
The length direction X-ray radiation restriction sections 14
include an upper length direction X-ray radiation restriction
section 14a and a lower length direction X-ray radiation
restriction section 14b which are longer in the lateral direction
and are respectively located above and below the output opening 12
as seen in a front view. The lateral direction X-ray radiation
restriction sections 15 include a left lateral direction X-ray
radiation restriction section 15a and a right lateral direction
X-ray radiation restriction section 15b which are longer in the
length direction and are respectively located to the left and to
the right of the output opening 12 as seen in a front view.
In FIG. 4, the lateral direction X-ray radiation restriction
sections 15 are located on the X-ray generation section 10 side
with respect to the length direction X-ray radiation restriction
sections 14. Alternatively, the length direction X-ray radiation
restriction sections 14 may be located on the X-ray generation
section 10 side with respect to the lateral direction X-ray
radiation restriction sections 15.
The X-ray radiation range restriction section driving section 16
includes blocking plate length direction moving mechanisms 16a and
blocking plate lateral direction moving mechanisms 16b. The
blocking plate length direction moving mechanisms 16a respectively
move the two length direction X-ray radiation restriction sections
14a and 14b, which are two blocking plates, in the length
direction. The blocking plate lateral direction moving mechanisms
16b respectively move the two lateral direction X-ray radiation
restriction sections 15a and 15b, which are two blocking plates, in
the lateral direction.
Each blocking plate length direction moving mechanism 16a acts as
follows. The length direction screw shaft 161a which is in screw
engagement with the screw groove 141 (to-be-guided member having a
female thread in an inner surface thereof), attached to the length
direction X-ray radiation restriction section 14 along the length
direction screw shaft 161a, is rotated by the length direction
positional adjustment motor 162a (162), and thus each length
direction X-ray radiation restriction section 14 is moved in the
length direction.
One of the blocking plate length direction moving mechanisms 16a is
located at an upper position in correspondence with the upper
length direction X-ray radiation restriction section 14a, and the
other blocking plate length direction moving mechanism 16a is
located at a lower position in correspondence with the lower length
direction X-ray radiation restriction section 14b. Therefore, the
upper length direction X-ray radiation restriction section 14a and
the lower length direction X-ray radiation restriction section 14b
can move in the length direction independently from each other.
The blocking plate length direction moving mechanisms 16a are
located offset in the lateral direction from the lateral-direction
center of the length direction X-ray radiation restriction sections
14 which are longer in the lateral direction. At a position offset
in the lateral direction from the lateral-direction center of the
length direction X-ray radiation restriction sections 14 in the
opposite direction, an inclination restriction shaft 143 is
provided. The inclination restriction shaft 143 is inserted through
inclination restriction holes 142 (to-be-guided members each having
a length direction through-hole) in correspondence with the upper
length direction X-ray radiation restriction section 14a and the
lower length direction X-ray radiation restriction section 14b.
Therefore, the length direction X-ray radiation restriction
sections 14 can be moved in the length direction by the blocking
plate length direction moving mechanisms 16a without being
inclined.
Each blocking plate lateral direction moving mechanism 16b acts as
follows. A lateral direction screw shaft 161b which is in screw
engagement with a screw groove 161 (to-be-guided member having a
female thread in an inner surface thereof), attached to the lateral
direction X-ray radiation restriction section 15 along the lateral
direction screw shaft 161b, is rotated by the length direction
positional adjustment motor 162a (162), and thus each lateral
direction X-ray radiation restriction section 15 is moved in the
lateral direction.
One of the blocking plate lateral direction moving mechanisms 16b
is located at a left position in correspondence with the left
lateral direction X-ray radiation restriction section 15a, and the
other blocking plate lateral direction moving mechanism 16b is
located at a right position in correspondence with the right
lateral direction X-ray radiation restriction section 15b.
Therefore, the left lateral direction X-ray radiation restriction
section 15a and the right lateral direction X-ray radiation
restriction section 15b can move in the lateral direction
independent from each other.
The blocking plate lateral direction moving mechanisms 16b are
located offset in the length direction from the length-direction
center of the lateral direction X-ray radiation restriction
sections 15 which are longer in the length direction. At a position
offset in the length direction from the length-direction center of
the lateral direction X-ray radiation restriction sections 15 in
the opposite direction, an inclination restriction shaft 153 is
provided. The inclination restriction shaft 153 is inserted through
inclination restriction holes 152 (to-be-guided members each having
a lateral direction through-hole) in correspondence with the left
lateral direction X-ray radiation restriction section 15a and the
right lateral direction X-ray radiation restriction section 15b.
Therefore, the lateral direction X-ray radiation restriction
sections 15 can be moved in the lateral direction by the blocking
plate lateral direction moving mechanisms 16b without being
inclined.
The length direction position adjusting motor 162a and a lateral
direction position adjusting motor 162b are each a positional
adjustment motor 162 and also a blocking driving source of the beam
formation mechanism 13.
The length direction X-ray radiation restriction sections 14 and
the lateral direction X-ray radiation restriction sections 15 are
included in an X-ray radiation range restriction section 13A.
As described above, the beam formation mechanism 13 includes the
length direction X-ray radiation restriction sections 14, the
lateral direction X-ray radiation restriction sections 15 and the
X-ray radiation range restriction section driving sections 16, and
is located forward with respect to the output opening 12 of the
X-ray generation section 10. Owing to this, the X-ray generated by
the X-ray generation section 10 is partially blocked to restrict
the X-ray radiation range thereof, and thus the X-ray cone beam Bx
directed toward the X-ray detection section 20 has a conical
shape.
This will be described in more detail. The distance between edges
14c, facing each other, of the upper length direction X-ray
radiation restriction section 14a and the lower length direction
X-ray radiation restriction section 14b is adjusted by the blocking
plate length direction moving mechanisms 16a, and the distance
between edges 15c, facing each other, of the left lateral direction
X-ray radiation restriction section 15a and the right lateral
direction X-ray radiation restriction section 15b is adjusted by
the blocking plate lateral direction moving mechanisms 16b. Thus,
an opening 17 having a square shape as seen in a front view that
forms the X-ray cone beam having a desired shape can be defined by
the edges 14c and the edges 15c.
The beam formation mechanism 13 having such a structure restricts
the radiation range of the X-ray cone beam Bx, generated by the
X-ray generator 10a, when the X-ray cone beam Bx passes the opening
17 formed by the X-ray cone beam Bx 13A. As described above, the
X-ray radiation range restriction section driving section 16 is
connected to the main body control section 60, and can restrict the
radiation range of the X-ray beam Bx to a desired range by use of
the X-ray radiation range restriction section driving control
section 60f.
The X-ray cone beam Bx is not limited to having a conical
shape.
For example, the number of the X-ray radiation restriction sections
may be increased so that the X-ray cone beam Bx has a cross-section
perpendicular to the radiation axis thereof that is pentagonal or
of a polygonal shape having more than five sides. Alternatively,
the structure of a diaphragm of a well-known camera that performs
visible light imaging may be adopted to block the X-ray such that
the X-ray beam Bx has a cross-section perpendicular to the
radiation axis thereof that is of a circular shape having a
variable diameter. In this case, the three-dimensional shape of the
X-ray CT imaging area may be spherical.
The X-ray imaging device 1 may include the cephalostat 43 as shown
in FIG. 2. This will be described in more detail. The cephalostat
43 is attached to, for example, an arm 501 extending horizontally
from an intermediate position of the support pillar 50. The
cephalostat 43 includes a fixing tool 431 that fixes the head of a
human body at a fixed position and an X-ray detector 432 usable for
cephalo imaging. The cephalostat 43 may be a cephalostat disclosed
in Japanese Laid-Open Patent Publication No. 2003-245277 or any of
various types of cephalostats.
Now, the imaging area setting screen 600 displayed as the X-ray
radiation range specification section 62a on the operation panel 62
will be described. As shown in FIG. 5, the imaging area setting
screen 600 is a screen to set a CT imaging area CA encompassing an
imaging target site OB. The imaging area setting screen 600
includes an image display section 610 that displays a dental arch
image 611, an upper/lower jaw selection section 620, a selection
range setting section 630, and a condition setting section 640.
The CT imaging area CA as seen in the Z-axis direction can be set
to have a shape covering a part of the dental arch.
The shape covering a part of the dental arch DA can be set to have
any range in accordance with the purpose of imaging the teeth
included in the dental arch DA or jaw bone. For example, as shown
in FIG. 5(a), the CT imaging area CA may have a perfectly circular
shape.
Alternatively, as shown in FIG. 5(b), the CT imaging area CA may
have an elliptical shape.
A perfectly circular CT imaging area CA and an elliptical CT
imaging area CA are both suitable to perform CT imaging on a local
imaging target site in the dental arch DA. A perfectly circular CT
imaging area CA has an advantage of simplifying the mechanical
control performed by the imaging mechanism 3 during the CT imaging.
In the case where the imaging target site has a lengthy shape
extending along a curved part of the dental arch DA, an elliptical
CT imaging area CA has an advantage of suppressing the X-ray
exposure dose of the subject M1 to a necessary but minimum possible
level.
In the case where, for example, the imaging target site encompasses
about four or less molar teeth, preferably about three or less
molar teeth, a perfectly circular CT imaging area CA suppresses the
unnecessary X-ray exposure dose to an extremely low level because
the area encompassed by the CT imaging area CA other than the teeth
is small.
The CT imaging area CA may have a shape shown in FIG. 5 (c).
In FIG. 5(c), the profile of the CT imaging area has an outer part
which is curved along a curved part of the dental arch DA and a
straight or generally straight inner part which connects both of
two ends of the curved outer part.
The CT imaging area CA having such a shape suppresses the X-ray
exposure dose of the subject M1 to a necessary but minimum possible
level.
In the case where the CT imaging area CA has the shape shown in
FIG. 5(b) or FIG. 5(c), the lateral direction X-ray radiation
restriction sections 15 (15a, 15b) are driven during the CT imaging
to adapt the width of the X-ray cone beam Bx in the x-axis
direction to the width of the CT imaging area CA in accordance with
the revolving angle of the revolving arm 30.
The X-ray imaging device 1 may perform CT imaging with on the CT
imaging area CA of only one of the shapes shown in FIG. 5(a)
through FIG. 5(c). Alternatively, the X-ray imaging device 1 may
perform CT imaging on the CT imaging area CA of all the shapes
shown in FIG. 5(a) through FIG. 5(c) so that one of the shapes can
be selected by mode switching.
In FIG. 5(a), the image display section 610 displays a
specification cursor (pointer) 612 that specifies the center of the
CT imaging area CA and a CT imaging area line 613 that defines a
perfect circle having the center specified by the specification
cursor 612 and a radius specified by the selection range setting
section 630 described later. The specification cursor 612 and the
CT imaging area line 613 are displayed as overlapping the dental
arch image 611.
The upper/lower jaw selection section 620 includes an UPPER button
621 to set the CT imaging area CA on the upper jaw, a FULL button
622 to set the CT imaging area CA on both of the upper jaw and the
lower jaw, and a LOWER button 623 to set the CT imaging area CA on
the lower jaw.
The selection range setting section 630 includes a text box 631
usable to input a radius from the center specified by the
specification cursor 612. Alternatively, the selection range
setting section 630 may be usable to input a diameter.
The condition setting section 640 includes a Set button 641, a
Reset button 642, a Next button 643, a Mode button 644, and a
Return button 645.
The Set button 641 is an operation button to save the settings on
the CT imaging area CA made by the image display section 610, the
upper/lower jaw selection section 620 and the selection range
setting section 630 (for performing a setting operation accepting
step s12).
The Reset button 642 is an operation button to reset the settings
on the CT imaging area CA made by the image display section 610,
the upper/lower jaw selection section 620 and the selection range
setting section 630.
The Next button 643 is an operation button to change the imaging
area setting screen 600 to the high sensitivity site specification
screen 700 to set a high sensitivity area H described later based
on the settings saved by the Set button 641.
The Mode button 644 is an operation button to select any of various
modes. More specifically, the Mode button 644 is usable to switch a
perfect circle mode to set the CT imaging area CA to a perfect
circle to an ellipse mode to set the CT imaging area CA to an
ellipse or vice versa, or that selects a panorama mode to perform
panorama imaging.
The "panorama imaging" refers to panorama X-ray imaging. The
panorama image obtained by the panorama X-ray imaging is a panorama
X-ray image.
The Return button 645 is an operation button to return the imaging
area setting screen 600 to an initial screen (not shown).
The display section 61 acts as an operation display section. When
CT imaging is to be performed on an imaging target site, first, the
imaging area setting screen 600 provided on the display section 61
accepts an operation of setting the CT imaging area line 613
encompassing the imaging target site OB.
This will be described in more detail. One of the buttons in the
upper/lower jaw selection section 620 is pressed to indicate
whether the imaging target site OB is in the upper jaw, the lower
jaw or both of the upper jaw and the lower jaw. The specification
cursor 612 is operated on the dental arch image 611 shown in the
image display section 610 of the imaging area setting screen 600 to
specify the center of a circle defining the CT imaging area CA. A
value of the radius of the circle is input to the text box 631 of
the selection range setting section 630.
Specification operation information, based on the center of the
circle defining the CT imaging area CA which is input to the
imaging area setting screen 600 and the value of the radius which
is input to the text box 631, is transmitted to the information
processing device 8. Upon receipt of the specification operation
information, the information processing device 8 transmits the
information on the CT imaging area line 613 to the operation
display section 61. Upon receipt of the information on the CT
imaging area line 613, the operation display section 61 displays
the CT imaging area line 613 based on the received information as
overlapping the dental arch image 611 in the image display section
610 of the imaging area setting screen 600.
Upon checking the imaging area setting screen 600, the operator
confirms that the CT imaging area line 613 is set to a desired
position and a desired range on the dental arch image 611. When the
Set button 641 is pressed, the CT imaging area line 613 is
transmitted as a circle defining the CT imaging area CA to the
information processing device 8. When the Next button 643 is
pressed, the imaging area setting screen 600 is changed to the high
sensitivity site specification screen 700 described later.
In the above description, a numerical value of the radius
indicating the size of the CT imaging area CA is input to the text
box 631. Alternatively, the size of the CT imaging area CA may be
adjusted as follows. The CT imaging area line 613 defining a
perfect circle centered around the point specified by the
specification cursor 612 is displayed as overlapping the dental
arch image 611, and a point on the CT imaging area line 613 is held
by the specification cursor 612 to adjust the size of the CT
imaging area CA.
The X-ray imaging device 1 may be structured such that the mode is
switched when the specification cursor 612 is operated to change
the shape of the CT imaging area line 613. For example, the X-ray
imaging device 1 may be structured such that the perfect circle
mode is changed to the ellipse mode when the specification cursor
612 is operated to change the shape of the CT imaging area line 613
from a perfect circle to an ellipse.
In this manner, a perfectly circular CT imaging area CA can be set
on, for example, a local imaging target site OB including two or
three left molars. Therefore, an X-ray can be directed to only the
imaging target site OB, which is an area of interest, in a limited
manner, and also the CT imaging area CA can be set on a desired
area.
The CT imaging area CA can be set to have any of various shapes
instead of a perfect circle. In accordance with the size or range
of the imaging target site OB as an area of interest, or the
position of the imaging target site OB in the dental arch DA, the
CT imaging area CA can be set to have an elliptical, generally
triangular, oval or any of various other shapes along the curved
shape of the dental arch DA. Owing to this, the imaging target site
OB as an area of interest can be imaged with certainty while the
unnecessary X-ray exposure dose is decreased. In addition, the
imaging target site OB determined based on the diagnosis, the
symptom or the like is prevented as much as possible from being
unnecessarily exposed to the X-ray, and the applicability of the
X-ray imaging device 1 can be improved.
Now, the high sensitivity site specification screen 700 displayed
as the high sensitivity site setting section 62b on the operation
panel 62 will be described. As shown in FIG. 6, the high
sensitivity site specification screen 700 is a screen to set a high
sensitivity site H with respect to the CT imaging area CA set on
the imaging area setting screen 600. The high sensitivity site
specification screen 700 includes an image display section 710 that
displays a high sensitivity site H, a property display section 720
that displays detailed information on the high sensitivity site H,
and a condition setting section 730.
The image display section 710 displays a high sensitivity site side
image 711 that shows the high sensitivity site H on a side view
image of the subject M1, a specification cursor (pointer) 712 that
specifies the high sensitivity site H displayed as overlapping the
high sensitivity site side image 711, and a planar direction
cross-sectional view image 713. The planar direction
cross-sectional view image 713 shows a cross-sectional view of the
subject M1, in a planar direction, encompassing the high
sensitivity site H specified by the specification cursor 712.
The high sensitivity site side image 711 and the planar direction
cross-sectional view image 713 are each an example of high
sensitivity specification image that specifies a high sensitivity
specification H. Preferably, the high sensitivity site side image
711 and the planar direction cross-sectional view image 713 are
each a schematic illustration or the like of the head of the
subject M1. The size and shape of the head is based on the size and
shape of a head having a standard bone structure. An internal
structure including hard tissue and important soft tissue may be
illustrated to some extent.
As the high sensitivity site side image 711 or the planar direction
cross-sectional view image 713, a plurality of high sensitivity
site specification images may be prepared for various body sizes.
Alternatively, a plurality of high sensitivity site specification
images may be prepared for adults and children or for men and
women.
The high sensitivity site specification image may be an X-ray image
acquired by actually imaging the subject M1 or may be a schematic
illustration or the like of the head of the subject M1. In the
latter case, there is an advantage that the subject M1 is prevented
from being exposed to the X-ray.
In FIG. 6, the high sensitivity site side image 711 shows parotid
gland Ha and submandibular gland Hb as the high sensitivity sites
H. Since the specification cursor 712 specifies the parotid gland
Ha, the planar-direction cross-sectional view image 713 shows the
parotid gland Ha. The cross-sectional view image 713 shows the CT
imaging area CA set on the imaging area setting screen 600 together
with right and left parotid gland Har and Hal. When the
specification cursor 712 specifies the submandibular gland Hb in
the high sensitivity site side image 711, the planar-direction
cross-sectional view image 713 shows the submandibular gland Hb.
The specification cursor 712 may specify the high sensitivity site
H shown in the cross-sectional view image 713.
The high sensitivity site side image 711 may be an image of the
head seen from a lateral side, from the front side or at any other
angle. The high sensitivity site side image 711 may include images
seen at a plurality of angles, for example, images seen from a
lateral side and the front side.
Alternatively, one of the high sensitivity sites H shown in the
high sensitivity site side image 711 may be retrieved and displayed
independently.
As shown in FIG. 6, the high sensitivity site side image 711 may
show the dental arch DA or the CT imaging area CA in an overlapping
manner.
The X-ray imaging device 1 may be structured such that even without
the operator specifying the high sensitivity site H in the high
sensitivity site side image 711, all the registered high
sensitivity sites H are shown in the planar direction
cross-sectional view image 713.
The planar direction cross-sectional view image 713 may show only a
high sensitivity site H which is at the same level as the CT
imaging area CA. In this case, even when the operator specifies the
submandibular gland Hb in the high sensitivity site side image 711,
the planar direction cross-sectional view image 713 does not show
the submandibular gland Hb unless the submandibular gland Hb is at
the same level as the CT imaging area CA.
The property display section 720 displays the detailed information
on the high sensitivity site H specified, for example, in the high
sensitivity site side image 711 or by the specification cursor 712.
In more detail, the property display section 720 includes a name
display section 721 that displays a name of the high sensitivity
site H specified by the specification cursor 712, a priority level
setting and display section 722 to set or display a priority level
of the high sensitivity site H, a major axis setting and display
section 723 to set or display the length of a major axis among
various factors representing the size of the high sensitivity site
H as seen in the Z-axis direction, and a minor axis setting and
display section 724 to set or display the length of a minor axis of
the high sensitivity site H.
The priority level setting and display section 722, the major axis
setting and display section 723 and the minor axis setting and
display section 724 each have a text box, in which a priority level
or length based on preset information is stored and displayed. In
order to change such a priority level or length, another priority
level of length can be directly input to the text box.
The condition setting section 730 includes a Set button 731, a
Reset button 732, a Start button 733, a FreeStart button 734, and a
Return button 735.
The Set button 731 is an operation button to save the high
sensitivity site H specified by the specification cursor 712 and
the detailed information on the high sensitivity site H set and
displayed in the property display section 720.
The Reset button 732 is an operation button to reset the
specification of the high sensitivity site H specified by the
specification cursor 712 and the detailed information set and
displayed in the property display section 720.
The Start button 733 is an operation button to instruct start of CT
imaging on the CT imaging area CA based on the settings saved by
the Set button 731.
The FreeStart button 734 is an operation button to start CT imaging
with no consideration of the high sensitivity site H although the
high sensitivity site H located in the vicinity of the CT imaging
area CA which is specified by the imaging area setting screen 600
is shown in the high sensitivity site side image 711 or the
cross-sectional view image 713.
The Return button 735 is an operation button to return the high
sensitivity site specification screen 700 to an initial screen (not
shown)
The imaging area setting screen 600 may act as the revolving arm
trajectory setting section 60b. In this case, the high sensitivity
site H is displayed as overlapping the dental arch image 611.
The X-ray imaging device 1 may allow the operator to specify a
desired position as a high sensitivity site H. The X-ray imaging
device 1 may allow the operator to input a range of the high
sensitivity site H. For example, the X-ray imaging device 1 may be
structured such that even the high sensitivity site specification
screen 700, or the imaging area setting screen 600 acting as the
revolving arm trajectory setting section 60b, may allow the
operator to set a high sensitivity site H by drawing the high
sensitivity site H with a stylus or the like in the image display
section 710 or the image display section 610.
Hereinafter, with reference to FIG. 7, a method for performing CT
imaging on an imaging target site OB such that the exposure dose of
the high sensitivity site H is decreased by use of the X-ray
imaging device 1 having the above-described structure will be
described in detail.
The dental arch DA includes the teeth on the front side including
anterior teeth, teeth on the left molar side including left molar
teeth, and teeth on the right molar side including right molar
teeth. In the following example, one of the left molar teeth in the
dental arch DA is the imaging target site OB.
In the following example, the submandibular gland Hb is the high
sensitivity site H, the exposure dose of which is controlled to be
decreased.
First, for performing the CT imaging, the subject M1 is fixed with
respect to the main body part 2 accommodated in the X-ray-proof
chamber 70 by use of the subject holding section 421.
In this state, the imaging area setting screen 600 is displayed on
the display section 61 by an operation made by the operator, so
that an imaging mode is selectable by use of the Mode button 644
(step s1). When the Mode button 644 displayed on the imaging area
setting screen 600 is pressed to select the panorama mode (step s2:
Yes), the X-ray imaging device 1 performs panorama imaging on the
subject M1 (step s3).
For performing the panorama imaging, the X-ray imaging device 1
controls, by use of the main body control section 60, the X-ray
radiation range restriction section driving sections 16 that
controls the driving of the beam formation mechanism 13. The
control is performed such that the distance between the edges 14c
of the upper length direction X-ray radiation restriction section
14a and the lower length direction X-ray radiation restriction
section 14b is adjusted to be long, and such that the distance
between the edges 15c of the left lateral direction X-ray radiation
restriction section 15a and the right lateral direction X-ray
radiation restriction section 15b is short. In this way, the
opening 17 is put into a rectangular shape longer in the length
direction as seen in a front view. Thus, an X-ray slit beam having
a conical shape longer in the length direction is directed toward
the X-ray detection section 20 and the panorama imaging is
performed.
Alternatively, there may be the following case. In the imaging area
setting screen 600, the Mode button 644 is not pressed or the Mode
button 644 is pressed to select an ellipse mode or a perfect circle
mode (step s2: No). In the dental arch image 611 in the image
display section 610, the imaging target site OB is set by the
specification cursor 612. A numerical value is input to the text
box 631 in the selection range setting section 630. The Next button
643 is pressed and the setting on a CT imaging area CA is accepted
(step s4). In this case, the X-ray imaging device 1 displays the
high sensitivity site specification screen 700 in the display
section 61.
When, on the high sensitivity site specification screen 700, the
FreeStart button 734 is pressed, or no high sensitivity site H is
specified by the specification cursor 712 and the Start button 733
is pressed (step s5: No), it is determined that the exposure dose
does not need to be decreased and common CT imaging is performed
(step s6).
For forming the CT imaging area CT set on the imaging area setting
screen 600 in such common CT imaging, the X-ray imaging device 1
controls, by use of the main body control section 60, the X-ray
radiation range restriction section driving sections 16 that
controls the driving of the beam formation mechanism 13. The
control is performed such that the distance between the length
direction X-ray radiation restriction sections 14, and the distance
between the lateral direction X-ray radiation restriction sections
15, are short. In this way, the opening 17 is put into a square
shape, as seen in a front view, smaller than the shape in the case
where common large viewfield CT imaging is performed. Thus, an
X-ray cone beam for a small viewfield that has a conical shape is
directed toward the X-ray detection section 20. In addition, as
shown in FIG. 8 and FIG. 9, the elevation section 41a is controlled
to adjust the height of the revolving arm 30 with respect to the
imaging target site OB of the subject M1. Thus, the CT imaging on a
small viewfield is performed.
This will be described in more detail. Referring to FIG. 8, when
the imaging target site OB is in the upper jaw, the main body
control section 60 raises the revolving arm 30 in the Z-axis
direction from the position of the revolving arm 30 for common
large viewfield CT imaging (represented by the dashed line). At
this position in the height direction, the revolving arm 30 is
revolved to perform the CT imaging on the imaging target site OB in
the upper jaw.
By contrast, referring to FIG. 9, when the imaging target site OB
is in the lower jaw, the main body control section 60 lowers the
revolving arm 30 in the Z-axis direction from the position of the
revolving arm 30 for common large viewfield CT imaging (represented
by the dashed line) and also from the position of the revolving arm
30 when the imaging target site OB is in the upper jaw. At this
position in the height direction, the revolving arm 30 is revolved
to perform the CT imaging on the imaging target site OB in the
lower jaw.
The common CT imaging performed in step S6 may be performed on a
large viewfield instead of a small viewfield described above.
The CT imaging area CA of a large viewfield may cover the entire
head, the entire jaw bone or the entire dental arch, in the
horizontal direction.
The X-ray imaging device 1 may be structured such that one of CT
imaging on a large viewfield and CT imaging on a small viewfield is
selectable. Alternatively, the X-ray imaging device 1 may be
structured such that one of CT imaging on a large viewfield, CT
imaging on a small viewfield, and CT imaging on a single or a
plurality of middle viewfields between the small viewfield and the
large viewfield is selectable. Still alternatively, the X-ray
imaging device 1 may be structured such that any size of viewfield
between the small viewfield and the large viewfield can be selected
with no stage being set.
The X-ray imaging device 1 may be structured such that any size of
viewfield may be set between the small viewfield and the middle
viewfield with no stage being set, or such that CT imaging is
performed only on a middle viewfield.
In the above example, the main part control section 60 controls the
X-ray radiation range restriction section driving sections 16 to
drive the beam formation mechanism 13 so that an X-ray cone beam Bx
for a small viewfield is formed by the opening 17 having a small
square shape as seen in a front view. Alternatively, the main body
control section 60 may control the revolution shaft moving section
30m of the revolving arm driving section 30K such that the X-ray
generation section 10 including the X-ray generator 10a approaches
the subject M1. As a result of this, the X-ray cone beam Bx
directed toward the imaging target site OB has a smaller
cross-section, and the CT imaging is performed on a small
viewfield.
By contrast to the CT imaging in which the exposure dose does not
need to be decreased, there may be the following case. In the high
sensitivity site specification screen 700, the submandibular gland
Hb is specified as the high sensitivity site H by the specification
cursor 712 (step s5: Yes), and the detailed information on the high
sensitivity site H is input to the property display section 720.
Alternatively, the Start button 733 is pressed without the detailed
information being input (step s7). In this case, it is determined
that the exposure dose of the submandibular gland Hb needs to be
decreased. The X-ray imaging device 1 calculates the necessity
degree of each of control on the revolution range L of the
revolving arm 30 and control on the revolution plane of the
revolving arm 30, based on the CT imaging area CA set on the
imaging area setting screen 600 and the submandibular gland Hb
specified on the high sensitivity site specification screen
700.
This will be described in more detail. The main body control
section 60 of the X-ray imaging device 1 makes a calculation to
find whether it is sufficient to perform either one of the
revolution range control and the revolution plane control or
whether both of the controls need to be performed, in order to
decrease the exposure dose of the submandibular gland Hb. The
revolution range control is to control the revolution start
position Ls and a revolution end position Le in the revolution
range L of the revolving arm 30. The revolution plane control is to
control the revolution plane based on the level in the height
direction of the revolving arm 30 and the inclination angle of the
revolving arm 30, namely, the radiation angle of the X-ray cone
beam, with respect to the subject M1. Such a calculation is
performed by use of the revolving arm trajectory setting section
60b and the revolving arm driving control section 60c based on the
position or size of the CT imaging area CA and the submandibular
gland Hb.
When it is found to be sufficient to perform one of the revolution
range control and the revolution plane control (step s8: No), and
when it is further found to be sufficient to perform the revolution
range control (step s9: Yes), the main body control section 60
calculates and sets the revolution start position Ls and the
revolution end position Le of the revolving arm 30 (step s10), and
controls the X-ray radiation range restriction section driving
sections 16 to adjust the beam formation mechanism 13 in accordance
with the CT imaging area CA (step s11). Thus, the CT imaging is
performed (step s12).
The X-ray imaging device 1 may be structured such that in the case
where the calculation results show that it is not necessary to
decrease the exposure dose and that it is sufficient to perform
common CT imaging based on the position and range of the CT imaging
area CA, the common CT imaging is automatically performed, or it
may be so notified.
This will be described in more detail. FIG. 10 shows a trajectory
of rotation of the X-ray cone beam Bx when the revolving arm 30
revolves over 180 degrees in the common CT imaging for which the
exposure dose of the high sensitivity site H does not need to be
decreased. Now, it is assumed as shown in FIG. 10 that the
revolution start angle of the revolving arm 30 at the revolution
start position Ls of the revolution range Land the revolution end
angle of the revolving arm 30 at the revolution end position Le are
always set to be the same angle regardless of the relationship
between the position of the CT imaging area CA and the position of
the high sensitivity site H.
In the example of FIG. 10, the revolution range L of the revolving
arm 30 shows the revolution range on the X-ray generation section
10 side.
In this state, as shown in FIG. 10, the left submandibular gland
Hbl is close to the CT imaging area CA which is set on a left part
of the dental arch DA. Therefore, the left submandibular gland Hbl
is irradiated with the X-ray cone beam Bx over 180 degrees in which
the revolving arm 30 revolves. The right submandibular gland Hbr,
which is farther from the CT imaging area CA than the left
submandibular gland Hbl, is passed by the X-ray cone beam Bx in a
first half and a second half of the revolution of the revolving arm
30, and is partially irradiated double.
FIG. 11 shows a trajectory of rotation of the X-ray cone beam Bx
when the revolution start position Ls of the revolution range L is
set to a position rightward and forward with respect to the
revolution start position Ls shown in FIG. 10. The revolution end
position Le is set to a position which is away from the revolution
start position Ls by 180 degrees. Such settings are provided in
order to decrease the exposure dose of the submandibular gland
Hb.
In the example shown in FIG. 10 and FIG. 11, the revolving arm 30
revolves over 180 degrees to perform the CT imaging. In order to
acquire a CT image having a better quality, it is preferable to
acquire projection data of at least 180 degrees on any position in
the CT imaging area CA.
In order to realize this, CT imaging may be performed as follows.
The X-ray cone beam Bx is directed to acquire projection data while
the revolving arm 30 is revolved over an angle which is a sum of
180 degrees and an expansion angle of the X-ray cone beam Bx as
seen in the Z-axis direction, namely, over an angle which is a sum
of 180 degrees and a fan angle. As the revolution range L of the
revolving arm 30 is larger, the probability that the X-ray cone
beam Bx is directed to the high sensitivity site H is higher.
However, the X-ray exposure dose can be decreased by the
above-described structure.
This will be described specifically. As shown in FIG. 11, the
revolution start position Ls of the revolution range L is set to a
position rightward and forward with respect to the revolution start
position Ls shown in FIG. 10, based on the CT imaging area CA and
the submandibular gland Hb. In this case, the left submandibular
gland Hbl is close to the CT imaging area CA like in the case where
the common CT imaging is to be performed with no control on the
exposure dose. However, the right submandibular gland Hbr, which is
away from the CT imaging area CA, is prevented from being
irradiated double with the X-ray cone beam Bx. Therefore, the
exposure dose of the right submandibular gland Hbr can be
decreased.
This will be described in more detail. Referring to FIG. 12, when
CT imaging is to be performed with the X-ray cone beam Bx directed
from the X-ray generator 10a of the X-ray generation section 10
toward the X-ray detection section 20, more specifically, the X-ray
detector 20a, the X-ray cone beam Bx revolves about the imaging
target site OB in the CT imaging area CA. When seen in an axial
direction of the revolution shaft 31, the X-ray cone beam Bx can be
divided into an area g between the X-ray generator 10a and the CT
imaging area CA and an area d between the X-ray detection section
20 and the CT imaging area CA.
Referring to FIG. 13, when the X-ray cone beam Bx is revolved over
180 degrees to perform CT imaging, an area G is formed by the
trajectory of the area g whereas an area D is formed by the
trajectory of the area d. The area GD in which the area G and area
D overlap each other is formed.
When the submandibular glands Hb (Hbl, Hbr) are specified as the
high sensitivity sites H, the trajectory of the X-ray generator 10a
of the X-ray generation section 10 and the trajectory of the X-ray
detection section 20 (namely, the trajectory of the revolving arm
30) are set such that the area GD is offset from the submandibular
glands Hb (Hbl, Hbr).
As can be seen, the revolution range control of controlling the
trajectory of the revolving arm 30, namely, the revolution range L
of the revolving arm 30 merely needs to be performed such that the
area GD is offset from the submandibular glands Hb (Hbl, Hbr).
Thus, the revolution range control has a certain degree of freedom.
In consideration of the imaging efficiency, the revolution range
control may be performed as follows.
The subject M1 is guided into the X-ray-proof chamber 70 in the
state where the revolving arm 30 is at a wait position thereof,
which is usually set commonly to all the modes. A position which
has the shortest distance from the wait position, in such an area
that the area GD is offset from the submandibular glands Hb (Hbl,
Hbr), is set as the revolution start position Ls. The standby
switch 65a is operated to move the revolving arm 30 from the wait
position to the revolution start position Ls. Then, the imaging
actuation switch 65b is operated to revolve the revolving arm 30
over 180 degrees. Thus, the CT imaging is performed.
The revolution range L of the revolving arm 30 is set in this
manner, so that the wait time of the subject M1 for the CT imaging
can be shortened.
Referring to FIG. 8, when the X-ray imaging device 1 has a
mechanical structure in which the subject M1 is to face the support
pillar 50, the subject M1 is often guided to move toward the
support pillar 50 when entering the X-ray-proof chamber 70.
When exiting the X-ray-proof chamber 70, the subject M1 is often
guided to move away from the support pillar 50.
Therefore, the common wait position of the revolving arm 30 is
often set to the revolution start position Ls as shown in FIG. 10,
or the orientation of the ran 30 is slightly inclined from the
inclination when the revolving arm 30 is at the revolution start
position Ls. In either case, neither the X-ray generation section
10 nor the X-ray detection section 20 obstructs entrance of the
subject M1.
Oppositely, the revolution end position L3 of the revolving arm 30
is often set such that neither the X-ray generation section 10 nor
the X-ray detection section 20 obstructs exit of the subject
M1.
Preferably in the X-ray imaging device 1, the wait position of the
revolving arm 30 when the subject M1 enters the X-ray-proof chamber
70 and the revolution end position Le when the subject M1 exits the
X-ray-proof chamber 70 are set such that at least one of the
entrance and the exit of the subject M1 is made with no obstruction
by the X-ray generation section 10 or the X-ray detection section
20.
When no high sensitivity site H is specified, the CT imaging may be
performed from the common wait position.
As described above, the X-ray imaging device 1 is structured such
that the wait time of the subject M1 for the CT imaging can be
shortened. Therefore, the CT imaging can be performed with the
entrance or the exit of the subject M1 being not much obstructed
and with a short wait time.
The control of setting the revolution range L may be performed
manually by the operator. Alternatively, candidate areas in
accordance with the specified submandibular glands Hb may be stored
on the storage section 64.
The trajectory of the revolving arm 30, namely, the revolution
range L of the revolving arm 30 may be calculated each time based
on the specified high sensitivity site H. Alternatively, a table
may be stored on the storage section 64, so that the revolution
range L can be found automatically.
In the structure of the X-ray imaging device 1, the subject M1,
namely, the test subject, is positioned to face the support pillar
50. There is no specific limitation on the positional relationship
between the orientation of the subject M1 and the support pillar
50.
For example, the X-ray imaging device 1 may be structured such that
the support pillar 50 is located to the side of, namely, to the
left of, or to the right of, the subject M1.
In this example, as shown in FIG. 8, the X-ray imaging device 1 is
structured such that the subject M1 faces the support pillar 50.
Alternatively, for example, the X-ray imaging device 1 may be
structured such that the support pillar 50 is located to the left
of the subject M1 when seen in a front view, namely, is located to
the right of the subject M1 when seen in a rear view.
Still alternatively, the support pillar 50 and the elevation
section 41a may be omitted. In this case, for example, an arm-like
support member having one end fixed to the wall and extending
horizontally from the wall may be used. The revolution shaft 31 of
the revolving arm 30 may be axially supported by the other end of
the arm-like support member.
In any structure, it is preferable that the wait position of the
revolving arm 30 and the revolution end position Le are set such
that at least one of the entrance and the exit of the subject M1 is
made with no obstruction by the X-ray generation section 10 or the
X-ray detection section 20.
As described above, the X-ray imaging device 1 is structured such
that the wait time of the subject M1 for the CT imaging can be
shortened. Therefore, the CT imaging can be performed with the
entrance or the exit of the subject M1 being not much obstructed
and with a short wait time.
In the CT imaging in which the exposure dose of the submandibular
gland Hb dose needs to be decreased, there may be the following
case. A calculation is made to find whether it is sufficient to
perform either one of the revolution range control and the
revolution plane control is necessary or whether both of the
controls need to be performed, based on the CT imaging area CA set
on the imaging area setting screen 600 and the submandibular gland
Hb specified on the high sensitivity site specification screen 700.
When it is found to be sufficient to perform one of the revolution
range control and the revolution plane control (step s8: No), and
when it is further found to be sufficient to perform the revolution
range control (step s9: NO), the main body control section 60
controls the revolution shaft moving section 30m and the elevation
section 41a of the revolving arm driving section 30K to adjust the
height and/or angle of the revolving arm 30 with respect to the
subject M1 (step s13). In addition, the main body control section
60 controls the X-ray detection section driving section 23 and the
X-ray radiation range restriction section driving sections 16 to
adjust the heights of the X-ray generation section 10 and the X-ray
detection section 20 (step s14), and controls the beam formation
mechanism 13 to partially block the X-ray and thus to adjust the
radiation direction of the X-ray cone beam Bx (step s15). Thus, the
CT imaging is performed (step s16).
The method of the above-described control in the case where CT
imaging is to be performed on the CT imaging area CA in the upper
jaw will be described. If the revolving arm 30 is revolved at the
height and radiation angle as shown in FIG. 8, the expose dose of
the parotid gland Ha is increased. Referring to FIG. 14, in order
to decrease the expose dose of the parotid gland Ha, the revolving
arm 30 is moved downward and the beam formation mechanism 13 is
adjusted such that the X-ray cone beam Bx is directed slightly
upward.
The X-ray detector 20a is moved upward or downward by the X-ray
detection section driving section 23 such that the X-ray detector
20a can receive the X-ray cone beam Bx even when the X-ray cone
beam Bx is directed upward or downward. In the state shown in FIG.
14, the X-ray cone beam Bx is directed slightly upward, and thus
the X-ray detector 20a is moved upward.
Alternatively, the X-ray detector 20a may have a large detection
surface in the up-down direction so that the X-ray detector 20a can
receive the X-ray cone beam Bx even when the X-ray cone beam Bx is
directed upward or downward. In this case, the X-ray detection
section driving section 23 may be omitted.
The method of the above-described control in the case where CT
imaging is to be performed on the CT imaging area CA in the lower
jaw will be described. If the revolving arm 30 is revolved at the
height and radiation angle as shown in FIG. 9, the expose dose of
the thyroid gland He (FIG. 15) is increased. Referring to FIG. 15,
in order to decrease the expose dose of the thyroid gland Hc, the
revolving arm 30 is moved upward and the beam formation mechanism
13 is adjusted such that the X-ray cone beam Bx is directed
slightly downward.
As long as the X-ray cone beam Bx is offset from the thyroid gland
Hc, it is not necessary to change the height of the revolving arm
30, the height of the X-ray detector 20a or the radiation direction
of the X-ray cone beam Bx during the CT imaging. When, for example,
it is wished that the X-ray cone beam Bx is not directed toward the
other high sensitivity sites H, the radiation direction of the
X-ray cone beam Bx may be moved upward or downward by the beam
formation mechanism 13, and the height of the X-ray detector 20a
may be changed by the X-ray detection section driving section 23 in
accordance with the position at which the X-ray cone beam Bx is
received, during the CT imaging.
As described above, the revolution plane control adjusts the height
of the revolving arm 30 with respect to the subject M1 and also
adjusts the radiation direction of the X-ray cone beam Bx, namely,
the inclination of revolution plane. Referring to FIG. 16, when the
X-ray cone beam Bx is directed from the front side of the head of
the subject M1, the radiation direction of the X-ray cone beam Bx,
namely, the revolution plane, is inclined upward in order to
decrease the exposure dose.
The X-ray imaging device 1 is also usable for otorhinology.
Referring to FIG. 17, it is now assumed that an area of the
auditory ossicles or the vicinity thereof is the CT imaging area CA
and the X-ray cone beam Bx is directed from the rear side of the
head of the subject M1. If the X-ray cone beam Bx is directed
horizontally, the lens Im of the eyeball I is on the radiation path
of the X-ray cone beam Bx. In order to decrease the exposure dose
of the lens Im, the radiation direction of the X-ray cone beam Bx,
namely, the revolution plane, is inclined downward.
In order to avoid distortion of images, it is preferable that the
X-ray cone beam Bx from the X-ray generation section 10 is
perpendicularly incident on the X-ray detection 20. Therefore, the
heights of the X-ray generation section 10 and the X-ray detection
section 20 are set such that the X-ray cone beam Bx is inclined at
a minimum possible angle at which the X-ray cone beam Bx is offset
from the high sensitivity site H.
In the case described above, it is sufficient to perform either one
of the revolution range control and the revolution plane control is
necessary. By contrast, there is a case where it is found that both
of the revolution range control and the revolution plane control
are necessary (step s8: Yes). In this case, the main body control
section 60 calculates and sets the revolution start position Ls and
the revolution end position Le (step s17). In addition, the main
body control section 60 controls the revolution shaft moving
section 30m and the elevation section 41a of the revolving arm
driving section 30K to adjust the height and/or angle of the
revolving arm 30 with respect to the subject M1 (step s18). The
main body control section 60 further controls the X-ray detection
section driving section 23 and the X-ray radiation range
restriction section driving sections 16 to adjust the heights of
the X-ray generation section 10 and the X-ray detection section 20
(step s19), and controls the beam formation mechanism 13 to
partially block the X-ray and thus to adjust the radiation
direction of the X-ray cone beam Bx (step s20). Thus, the CT
imaging is performed (step s21).
The X-ray imaging device 1 performs at least one of the revolution
range control and the revolution plane control based on the CT
imaging area CA set on the imaging area setting screen 600 and the
high sensitivity site H set on the high sensitivity site
specification screen 700, so that CT imaging is performed on the CT
imaging area CA with certainly while the exposure dose of the high
sensitivity site H is decreased.
In the above example, one high sensitivity site H displayed on the
high sensitivity site specification screen 700 in an overlapping
manner is specified for one CT imaging area CA, and the exposure
dose thereof is decreased. Hereinafter, a method for decreasing the
exposure dose of a plurality of high sensitivity sites H specified
for one CT imaging area CA will be described.
In the CT imaging in which the exposure dose of the submandibular
gland Hb needs to be decreased, there may be the following case. A
calculation is made to find whether it is sufficient to perform
either one of the revolution range control and the revolution plane
control is necessary or whether both of the controls need to be
performed, based on the CT imaging area CA set on the imaging area
setting screen 600 and the submandibular gland Hb specified on the
high sensitivity site specification screen 700. When it is found to
be sufficient to perform one of the revolution range control and
the revolution plane control (step s8: No), and when it is further
found to be sufficient to perform the revolution range control
(step s9: Yes), the process shown in FIG. 18 is performed. When one
high sensitivity site H is specified (step t1: No), the main body
control section 60 calculates and sets the revolution start
position Ls and the revolution end position Le of the revolving arm
30 (step t2) like in step s10. The steps after this are the same as
steps s11 and s12 and will not be described.
Now, it is assumed that a plurality of high sensitivity sites H
(Ha, Hb) are specified (step t1: Yes) and further that all the high
sensitivity sites H (Ha, Hb) can be offset from the revolution
trajectory of the X-ray cone beam Bx, namely, the area GD mentioned
above (step t3: Yes). In this case, the main body control section
60 calculates and sets the revolution start position Ls and the
revolution end position Le such that all the high sensitivity sites
H (Ha, Hb) are offset from the area GD (step t4). The steps after
this are the same as steps s11 and s12 and will not be
described.
By contrast, when the plurality of high sensitivity sites H (Hd,
Hb) cannot be all offset from the area GD (step t3: No), the main
body control section 60 calculates and sets the revolution start
position Ls and the revolution end position Le such that at least
one of the high sensitivity sites H (Hd, Hb) that has a high
priority level is offset from the area GD (step t5) as shown in
FIG. 19. In the example shown in FIG. 19, high sensitivity sites Hb
have a higher priority level than that of high sensitivity sites
Hd. The steps after this are the same as steps s11 and s12 and will
not be described.
When it is found to be sufficient to perform one of the revolution
range control and the revolution plane control (step s8: No), and
when it is further found to be sufficient to perform the revolution
plane control (step s9: No), the process shown in FIG. 20 is
performed. When one high sensitivity site H is specified (step u1:
No), the main body control section 60 adjusts the height and/or
angle of the revolving arm 30 like in step s13 (step u2), and also
adjusts the heights of the X-ray generation section 10 ands the
X-ray detection 20 such that the specified high sensitivity site H
is offset from the revolution trajectory of the X-ray cone beam Bx
(step u3). The steps after this are the same as steps s15 and s16
and will not be described.
Now, it is assumed that a plurality of high sensitivity sites H
(Hb, He) are specified (step u1: Yes) and further that all the high
sensitivity sites H (Hb, He) can be offset from the revolution
trajectory of the X-ray cone beam Bx, namely, the area GD mentioned
above (step u4: Yes) as shown in FIG. 21 and FIG. 22. In this case,
the main body control section 60 adjusts the height and/or angle of
the revolving arm 30 such that all the high sensitivity sites H
(Hb, He) are offset from the area GD (step u5), and also adjusts
the heights of the X-ray generation section 10 ands the X-ray
detection 20 such that all the high sensitivity sites H are offset
from the revolution trajectory of the X-ray cone beam Bx (step u6).
The steps after this are the same as steps s15 and s16 and will not
be described.
By contrast, when the plurality of high sensitivity sites H (Hb,
Hf, not shown) cannot be all offset from the area GD (step u4: No),
the main body control section 60 adjusts the height and/or angle of
the revolving arm 30 such that at least one of the high sensitivity
sites H (Hb, Hf) that has a high priority level is offset from the
area GD (step u7), and also adjusts the heights of the X-ray
generation section 10 ands the X-ray detection 20 such that the at
least one high sensitivity site H is offset from the revolution
trajectory of the X-ray cone beam Bx (step u8). The steps after
this are the same as steps s15 and s16 and will not be
described.
As described above, the X-ray imaging device 1 includes the
revolving arm 30 that revolves, about the revolution shaft 31, the
X-ray generator 10a and the X-ray detector 20a located to face each
other while having the subject M1, the revolution driving section
30s that revolves the revolving arm 30 with respect to the subject
M1, the imaging area setting screen 600 that accepts the setting of
a local area of the subject M1 as the CT imaging area CA, and the
main body control section 60 that controls at least the revolution
driving section 30s. The X-ray imaging device 1 revolves the
revolving arm 30 so as to direct the X-ray cone beam Bx toward the
CT imaging area CA to perform CT imaging. The X-ray imaging device
1 further includes the high sensitivity site specification screen
700 to specify a high sensitivity site H of a biological body that
is sensitive to X-rays from the area GD that revolves during the CT
imaging. The main body control section 60 controls at least one of
the X-ray revolution plane formed by the X-ray cone beam Bx along
with the revolution of the revolving arm 30 and the revolution
range L of the revolving arm 30 such that the X-ray exposure dose
of the high sensitivity site H specified on the high sensitivity
site specification screen 700 is decreased when the X-ray cone beam
Bx is directed toward the CT imaging area CA set on the imaging
area setting screen 600. (In this specification, the X-ray
revolution plane formed by the X-ray cone beam Bx will also be
expressed as the "X-ray revolution plane of the revolving arm 30".)
Owing to such a structure of the X-ray imaging device 1, even when
the high sensitivity site H is in the vicinity of the CT imaging
area CA which is set to encompass the imaging target site OB, the
imaging target site OB can be imaged with certainty while the
exposure dose of the high sensitivity site H is decreased. The
"local area" mentioned above is a part of the subject M1 and is
displayed as seen in the Z-axis direction.
This will be described in more detail. The main body control
section 60 controls at least one of the X-ray revolution plane
formed by the X-ray cone beam Bx along with the revolution of the
revolving arm 30 and the revolution range L of the revolving arm 30
such that the X-ray exposure dose of the high sensitivity site H
specified on the high sensitivity site specification screen 700 is
decreased when the X-ray cone beam Bx is directed toward the CT
imaging area CA set on the imaging area setting screen 600. Owing
to such a structure of the X-ray imaging device 1, even when the
high sensitivity site H is in the vicinity of the CT imaging area
CA, the imaging target site OB in the CT imaging area CA can be
imaged with certainty while the exposure dose of the high
sensitivity site H is decreased.
According to the control on the revolution range L performed by the
main body control section 60, at least one of the revolution start
position Ls and the revolution end position Le in the revolution
range L is changed in accordance with the CT imaging area CA set on
the imaging area setting screen 600 or the high sensitivity site H
specified on the high sensitivity site specification screen 700.
Owing to this, the revolution range L of the revolving arm 30 can
be adjusted without changing the X-ray revolution plane of the
revolving arm 30. Therefore, the exposure dose of the high
sensitivity site H specified on the high sensitivity site
specification screen 700 can be easily decreased.
According to the control on the revolution plane performed by the
main body control section 60, at least one of the X-ray radiation
angle with respect to a determined reference plane and the position
in the subject M1 to be irradiated with the X-ray is changed in
accordance with the CT imaging area CA set on the imaging area
setting screen 600 or the high sensitivity site H specified on the
high sensitivity site specification screen 700. Owing to this, the
imaging target site OB in the CT imaging area CA can be imaged with
certainty while the exposure dose of the high sensitivity site H in
the vicinity of the imaging target site OB is decreased. The
"reference plane" may be, for example, a plane expanding in the
horizontal direction at a specific height.
The X-ray imaging device 1 includes the top frame 41 that supports
the revolving arm 30 via the revolution shaft 31. The upper frame
41 includes the revolution shaft moving section 30m that moves the
revolution shaft 31 with respect to the top frame 41, and the
elevation section 41a that moves the top frame 41 with respect to
the subject M1. The main body control section 60 controls the
movement of the revolution shaft moving section 30m and the
elevation section 41a to control the X-ray revolution plane. Owing
to such a structure, the top frame 41 that supports the revolving
arm 30 via the revolution shaft 31 can be moved by the elevation
section 41a, so that the exposure dose of the high sensitivity H
specified on the high sensitivity site specification screen 700 can
be easily decreased.
The beam formation mechanism 13 that restricts the X-ray radiation
range is provided forward to the X-ray generator 10a in the X-ray
radiation direction. The main body control section 60 controls the
restriction operation of the beam formation mechanism 13 to control
the X-ray revolution plane. Owing to this, the X-ray radiation
range restricted by the beam formation mechanism 13 can be changed,
so that the exposure dose of the high sensitivity H specified on
the high sensitivity site specification screen 700 can be easily
decreased.
The X-ray imaging device 1 includes the storage section 64 that
stores information on the high sensitivity site H. Owing to this,
information on the high sensitivity site H such as, for example,
the position, size, sensitivity degree, priority level (weighting
degree) or the like stored on the storage section 64 can be
retrieved. Thus, the CT imaging is performed in such a manner that
the exposure dose of the high sensitivity H is decreased.
The CT imaging area CA can be set on the dental arch image 611
displayed on the imaging area setting screen 600, and the high
sensitivity site H can be displayed as overlapping the image dental
arch image 611. Owing to this, the high sensitivity site H
displayed as overlapping the image dental arch image 611 can be
visually checked. Therefore, the high sensitivity site H, the
exposure dose of which is to be decreased during the CT imaging,
can be specified with more certainty.
The X-ray imaging device 1 includes the property display section
720 that changes the high sensitivity site H to be displayed in the
image display section 710. Owing to this, the CT imaging can be
performed in an appropriate manner in accordance with the situation
of the subject M1. For example, a higher priority level is assigned
to a high sensitivity site H which is far from the CT imaging area
CA but has abnormality occurring, instead of a high sensitivity
site H closest to the CT imaging area CA.
The X-ray imaging device 1 includes the standby switch 65a and the
imaging actuation switch 65b. The standby switch 65a revolves the
revolving arm 30 to the revolution start position Ls in the
revolution range L, which is different for each imaging target site
OB set on the imaging area setting screen 600. The imaging
actuation switch 65b revolves the revolving arm 30 while directing
the X-ray toward a set area (CT imaging area CA) to perform CT
imaging. Owing to this, for example, the standby switch 65a is
operated to revolve the revolving arm 30 to the revolution start
position Ls of the radiation range L to prepare for imaging, and
the imaging actuation switch 65b is operated to further revolve the
revolving arm 30 for CT imaging. Thus, CT imaging can be performed
in such a manner that the exposure dose of the high sensitivity
site H is decreased.
The X-ray imaging device 1 includes the revolving arm driving
section 30K that moves the revolving arm 30. The main body control
section 60 drives the revolving arm driving section 30K to move the
revolving arm 30. The control to revolve the revolving arm 30 by
the main body control section 60 and the control to move the
revolving arm 30 by the revolving arm driving section 30K are
performed at the same time, so that panorama X-ray imaging can be
performed. Owing to this, when a panorama image is needed, panorama
X-ray imaging can be performed with no need to prepare another
X-ray imaging device.
The X-ray imaging device may include the cephalostat 43 located
perpendicularly to the revolution shaft 31. In this case, when a
cephalogram is needed, cephalo X-ray imaging can be performed with
no need to prepare another X-ray imaging device.
The X-ray generation source according to one or more embodiments of
the present invention corresponds to the X-ray generator 10a in the
above-described embodiment;
the electric X-ray detector corresponds to the X-ray detection
section 20;
the revolution section corresponds to the revolving arm 30;
the X-ray radiation area corresponds to the CT imaging area CA;
the X-ray radiation area setting section corresponds to the imaging
area setting screen 600;
the control section corresponds to the main body control section
60;
the X-ray CT imaging device corresponds to the X-ray imaging device
1;
the X-ray flux corresponds to the X-ray cone beam Bx;
the area where the X-ray flux passes corresponds to the area
GD;
the high sensitivity site corresponds to the high sensitivity site
H, the parotid gland Ha, the left parotid gland Hal, the right
parotid gland Har, the submandibular gland Hb, the left
submandibular gland Hbl, the right submandibular gland Hbr, the
thyroid gland Hc, and the lens Im;
the high sensitivity site specification section corresponds to the
high sensitivity site specification screen 700;
the X-ray radiation start position corresponds to the revolution
start position Ls;
the X-ray radiation end position corresponds to the revolution end
position Le;
the support section corresponds to the top frame 41;
the support section moving section corresponds to the elevation
section 41a;
the shaft moving mechanism corresponds to the revolution shaft
moving section 30m;
the relative moving mechanism corresponds to the elevation section
41a;
the X-ray radiation range restriction section corresponds to the
beam formation mechanism 13;
the control pattern storage section and the high sensitivity site
information storage section correspond to the storage section
64;
the image containing the X-ray radiation area corresponds to the
dental arch image 611;
the high sensitivity site replacing section corresponds to the
property display section 720;
the X-ray imaging preparation switch corresponds to the standby
switch 65a;
the X-ray radiation switch corresponds to the imaging actuation
switch 65b;
the movement driving section corresponds to the revolving arm
driving section 30K; and
the cephalo-imaging head fixation device corresponds to the
cephalostat 43.
However, the present invention is not limited to the
above-described embodiment and may be carried out in any of various
other embodiments.
For example, in the above-described embodiment, the height of the
revolving arm 30 with respect to the subject M1 is adjusted to
control the revolution plane of the revolving arm 30.
Alternatively, the structure shown in FIG. 23 and FIG. 24 is
usable. The revolving arm 30 is supported by the top frame 41 and
is not movable in the Z-axis direction. The revolving arm 30 is
movable only in the X-axis direction and the Y-axis direction and
is revolvable. The height of a chair 5 on which the subject M1 sits
is controlled with respect to the revolving arm 30 so that the
height of the revolution plane of the revolving arm 30 with respect
to the subject M1 is adjusted.
In the above-described embodiment, the revolution range L extends
over about 180 degrees. Alternatively, in the case where the
exposure dose of the high sensitivity site H is to be decreased by
controlling the revolution plane, the revolution range L may extend
over about 360 degrees. Still alternatively, DVT imaging or
tomosynthesis imaging with no limitation on the revolution range L
may be performed.
In the above-described embodiment, the revolving arm 30 is revolved
in the horizontal direction. Alternatively, the revolving arm 30
may be inclined while being revolved.
In the above-described embodiment, the high sensitivity site H
displayed on the high sensitivity site specification screen 700 in
an overlapping manner is specified by the specification cursor 712
in accordance with the CT imaging area CA set on the imaging area
setting screen 600. Alternatively, a plurality of high sensitivity
sites H may be registered on the storage section 64 so that a high
sensitivity site H corresponding to the CT imaging area CA can be
automatically specified.
As described above, the control patterns performed by the main body
control section 60 may be stored on the storage section 64 as being
associated with each CT imaging area CA set on the imaging area
setting screen 600. Owing to this, the CT imaging can be performed
in such a manner that the exposure dose of the high sensitivity
site H is decreased by merely setting the CT imaging area CA by use
of the imaging area setting screen 600.
It is not absolutely necessary to display a high sensitivity site H
on the high sensitivity site specification screen 700 in an
overlapping manner. Alternatively, a high sensitivity site H may be
drawn on the high sensitivity site specification screen 700 with
the specification cursor 712 or the stylus.
The dental arch image 611 and the image displayed in the image
display section 710 may be a scout image, a panorama image, a
cephalo image, a schematic illustration or an optically captured
photo of the subject M1, or a combination thereof, although this
partially overlaps the above description.
Among the detailed information on the high sensitivity site H
specified on the a high sensitivity site specification screen 700,
the size or position thereof does not need to be input to the
property display section 720, but may be set to be changeable by an
operation such as drag or the like by use of the specification
cursor 712 or the stylus.
The display section 61 may display an X-ray dose such as an
irradiation dose, an exposure dose of the patient or the like which
is expected when CT imaging is performed.
The radiation dose of the X-ray cone beam Bx may be adjusted based
on the position of the X-ray cone beam Bx in the revolution range L
during the CT imaging in accordance with the specified high
sensitivity site H.
DESCRIPTION OF THE REFERENCE NUMERALS
1 . . . X-ray imaging device 10a . . . X-ray generator 13 . . .
Beam formation mechanism 20 . . . X-ray detection section 30 . . .
Revolving arm 30K . . . Revolving arm driving section 30m . . .
Revolution shaft moving section 30s . . . Revolving driving section
31 . . . Revolution shaft 41 . . . Top frame 41a . . . Elevation
section 43 . . . Cephalostat 60 . . . Main body control section 64
. . . Storage section 65a . . . Standby switch 65b . . . Imaging
actuation switch 600 . . . Imaging area setting screen 611 . . .
Dental arch image 700 . . . High sensitivity site specification
screen 720 . . . Property display section Bx . . . X-ray cone beam
CA . . . CT imaging area GD . . . Area H . . . High sensitivity
site Ha . . . Parotid gland Hal . . . Left parotid gland Har . . .
Right parotid gland Hb . . . Submandibular gland Hbl . . . Left
submandibular gland Hbr . . . Right Submandibular gland Hc . . .
Thyroid gland Im . . . Lens L . . . Revolution range Ls . . .
Revolution start position Le . . . Revolution end position M1 . . .
Subject
* * * * *